Treatment mode selection systems and laser catheter systems including same

ABSTRACT

The present disclosure relates generally to the use of medical devices for the treatment of vascular conditions. In particular, the present disclosure provides devices and methods for using laser-induced pressure waves created within a sheath to disrupt intimal and medial calcium within the vasculature. The present disclosure also provides treatment mode selection systems that may be used with such devices and methods.

CROSS REFERENCE TO RELATED APPLICATIONS

Not applicable.

FIELD

The present disclosure relates generally to the use of medical devicesfor the treatment of vascular conditions. In particular, the presentdisclosure provides materials and methods for using laser-inducedpressure waves to disrupt vascular blockages and to deliver therapeuticagents to the blockage area.

BACKGROUND

Arterial disease is a common disease that affects millions of Americans.Coronary artery disease (CAD) most often results from a condition knownas atherosclerosis, which generally manifests as the accumulation of awaxy substance on the inside of a subject's coronary arteries. Thissubstance, called plaque, is made of cholesterol, fatty compounds,calcium, and a blood-clotting material called fibrin. Similarly,peripheral artery disease (PAD) often results from the accumulation ofplaque on the inside of a subject's peripheral arteries, such as thearteries in a patient's arms, hands, legs and/or feet.

As the plaque builds up in either coronary arteries, peripheral arteriesand other arteries, the corresponding artery narrows and/or becomesstenotic, thereby making it more difficult for blood to flow through thearteries. As the size of the stenosis increases and the blockageworsens, blood flow slows and upon the formation of a total vascularocclusion, blood flow through the corresponding artery completely stops,which in turn may cause pain in the extremities and, in severe cases,gangrene, which may ultimately require amputation.

Balloon angioplasty and other transluminal medical treatments arewell-known and have been proven efficacious in the treatment of stenoticlesions at the core of CAD and/or PAD, as long as the artery is onlypartially blocked and not totally blocked. In a typical angioplastyprocedure to treat CAD, a catheter is inserted into the groin or arm ofa subject and guided forward through the aorta and into the coronaryarteries of the heart. The angioplasty catheter includes a balloon,which when placed within the partial occlusion, can be inflated, therebydilating the obstruction or restriction and increasing the size of thediameter of the artery to provides more typical blood flow therethrough.

Over time, a vascular occlusion, particularly a total occlusion, maycalcify and/or becomes fibrous, thereby decreasing the balloon's abilityto dilate the vascular occlusion. Certain types of catheters, such aselectrically-induced shockwave balloon catheters, may be used to breakthe calcified tissue. An electrically-induced shockwave balloon cathetermay include a liquid filled balloon and a one or more pairs ofelectrodes within the balloon. Upon creating a discharge across theelectrodes, plasma is produced, which results in the formation of one ormore vapor bubbles. The vapor bubbles created within the balloon causethe balloon to expand and contract. The expansion and contraction of theballoon creates a hydraulic force that transfers energy to the vascularocclusion and/or to the walls of the vessel in an amount sufficient todisrupt intraluminal calcium as well as calcium within the tissue layerof the vasculature (for example, calcium deposits). In addition toproducing vapor bubbles being upon the formation of plasma generated bythe electrical reaction in the liquid, shockwaves are also produced. Theshockwaves are transferred through the balloon and to the calcifiedvascular occlusion, and the shockwaves modify the calcified occlusion.

In the event a total stenotic occlusion forms, it may be difficult forthe balloon to enter the stenosis. Additionally, if a total occlusioncalcifies and/or become fibrous, thereby increasing the hardness ofocclusion, it may become even more difficult, if not impossible, topenetrate the occlusion and insert a balloon catheter. For example, theproximal and/or distal ends of the occlusion may become calcified to thepoint that “caps” or “calcified caps” are created, such that even anelectrically-induced shockwave balloon catheter may be unable topenetrate the calcified total occlusion because the balloon must bewithin and adjacent the occlusion in order to operate. And because theballoon within an electrically-induced shockwave balloon catheter istypically proximal the distal end of the electrically-induced shockwaveballoon catheter, it is unable to be inserted into or through thecalcified cap of the total occlusion.

SUMMARY

What is needed is a device that is capable of penetrating a calcifiedand/or fibrous vascular occlusion, particularly a calcified cap(s), anddisrupting at least a portion of the vascular occlusion as the devicepenetrates and traverses the total occlusion. What is also needed is adevice that is capable of delivering laser-induced pressure waves to thevascular occlusion in order to disrupt the calcified and/or fibrousportions without applying a hydraulic force thereto. These and otherneeds are addressed by the various aspects, embodiments, andconfigurations of the present disclosure.

The present disclosure provides a catheter comprising an outer sheathhaving a proximal end and a distal end, wherein the distal end comprisesa tip, an inner sheath may include at least one lumen, a proximal endand a distal end, wherein the inner sheath is disposed radially withinthe outer sheath, wherein the distal end of the inner sheath may bedisposed proximate the tip, thereby creating a cavity among the outersheath, inner sheath, one or more emitters disposed within the innersheath extending from a distal proximal portion of the inner sheath tothe distal end of the inner sheath and into the cavity, wherein aproximal end of the one or more emitters is coupled to a lasergenerator, and at least one emitter is disposed within the cavity.

A catheter according to paragraph [0009], wherein the catheter furthercomprises one or more liquid medium ports disposed about the sheath.

A catheter according to any of paragraphs [0009]-[0010], wherein theouter sheath is capable of expanding and contracting in the axialdirection.

A catheter according to any of paragraphs[0009]-[0011], wherein theouter sheath is constructed from the group consisting of a polymer,polymer with a coil or embedded with braid, polymer with an embeddedbraid and fluorinated ethylene propylene or lubricious flouropolymerliner, laser cut hypotube, tricoil or bicoil or any combination of theforegoing.

A catheter according to any of paragraphs [0009]-[0012], wherein thecatheter further comprises a shield axially disposed within the cavitybetween the distal end of the inner sheath and the tip.

A catheter according to any of paragraphs [0009]-[0013], wherein theshield comprises a proximal end and a distal end, wherein the shieldtapers from the proximal end to the distal end or the shield tapers fromthe distal end to the proximal end.

A catheter according to any of paragraphs [0009]-[0014], wherein the tipcomprises a proximal end and a distal end, wherein the tip has a solidconstruction along its longitudinal axis from its proximal end to itsdistal end.

A catheter according to any of paragraphs [0009]-[0015], wherein the tipcomprises an open construction at the distal end of the outer sheath.

A catheter according to any of paragraphs [0009]-[0016], wherein the tipcomprises a proximal end and a distal end, wherein the tip has a hollowconstruction along its longitudinal axis from its proximal end to itsdistal end.

A catheter according to any of paragraphs [0009]-[0017], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 300 nanometers to about 360 nanometers, atpulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

A catheter according to any of paragraphs [0009]-[0018], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of about 308 nanometers, at pulse durations between about 10nanoseconds and about 200 nanoseconds, and at frequencies between about1 pulse per second to about 100 pulses per second.

A catheter according to any of paragraphs [0009]-[0019], wherein totalenergy output for the at least one emitter is between about 1 to 300millijoules per millimeter squared (mJ/mm²).

A catheter according to any of paragraphs [0009]-[0020], wherein theliquid medium is contrast medium or contrast solution.

A catheter according to any of paragraphs [0009]-[0021], wherein theliquid medium is any one of iodine-containing contrast medium orgadolinium contrast medium.

A catheter according to any of paragraphs [0009]-[0022], wherein theliquid medium is configured to exhibit high absorption of light energyemitted from the at least one emitter at wavelengths of between about 1nanometer to about 1 millimeter, at pulse durations between about 1nanosecond to about 1 second, and at frequencies between about 1 pulseper second to about 5000 pulses per second.

A catheter according to any of paragraphs [0009]-[0023], wherein the atleast one emitter is one or more concentric emitters.

A catheter according to any of paragraphs [0009]-[0024], wherein the atleast one emitter is two or more single-fiber emitters.

A catheter according to any of paragraphs [0009]-[0025], wherein the atleast one emitter is configured to translate within the outer sheath.

A catheter according to any of paragraphs [0009]-[0026], wherein the tipcomprises a distal end and a flexible membrane at its distal end.

A catheter according to any of paragraphs [0009]-[0027], wherein theliquid medium is configured to absorb light energy, create a laserinduced pressure wave and/or vapor bubbles and/or cavitation events todisrupt a vascular occlusion, modify the vascular surface to enhancedrug absorption including but not limited to fracturing bothintraluminal calcium and calcium deposits within the vasculature, and/orto deliver a drug to an area around a vascular occlusion. Liquid mediumcan include contrast medium, including for example, iodine-containingcontrast medium or gadolinium contrast medium, as well as contrastsolutions comprising dye(s) and/or particle(s).

A catheter according to any of paragraphs [0009]-[0028], wherein theinner sheath further comprises a first guidewire lumen, and furthercomprising a sealable valve coupled to the outer sheath, the sealablevalve having a second guidewire lumen and a seal, whereupon introducinga guidewire into the first guidewire lumen and the second guidewirelumen and introducing liquid medium to the cavity, the liquid mediumactuates the seal within the valve and closes an opening between thevalve and the guidewire.

A catheter according to any of paragraphs [0009]-[0029], wherein thesealable valve further comprises an exterior wall and a flange disposedradially therein, wherein a gap exists between the exterior wall and theflange.

A catheter according to any of paragraphs [0009]-[0030], wherein thesealable valve comprises a proximal portion and a distal portion, andwherein the flange is disposed toward the proximal portion of thesealable valve.

A catheter according to any of paragraphs [0009]-[0031], wherein theproximal portion of the sealable valve is tubular.

A catheter according to any of paragraphs [0009]-[0032], wherein thedistal portion of the sealable valve is tapered radially inward from theexterior wall towards the second guidewire lumen.

A catheter according to any of paragraphs [0009]-[0033], wherein thesealable valve further comprises openings within the exterior wallextending toward the proximal portion.

A catheter according to any of paragraphs [0009]-[0034], wherein theflange is tapered radially inward towards the second guidewire lumen asthe flange progresses from the distal portion toward the proximalportion.

The present disclosure also provides a method for treating an occlusionwithin the vasculature of a subject, the method comprising positioning acatheter within vasculature of a subject, the catheter comprising anouter sheath having a proximal end and a distal end, wherein the distalend comprises a tip, an inner sheath having at least one lumen, aproximal end and a distal end, wherein the inner sheath is disposedradially within the outer sheath, wherein the distal end of the innersheath is disposed proximate the tip, thereby creating a cavity amongthe outer sheath, inner sheath and tip, a shield axially disposed withinthe cavity between the distal end of the inner sheath and the tip, oneor more emitters disposed within distal end of the inner sheath and/orthe cavity, wherein one or more of the emitters is coupled to a lasergenerator, wherein the one emitter is disposed within the cavity, andone or more liquid medium ports coupled to the at least one lumen,positioning the tip adjacent an occlusion within the vasculature,introducing a liquid medium into the cavity through the one or moreliquid medium ports, activating the at least one emitter within thecavity to transmit pulses of light energy into the liquid medium,wherein transmitting the pulses of light energy from the emitter intothe liquid medium generates at least one propagating laser-inducedpressure waves that cause the tip to engage and disrupt at least aportion of the vascular occlusion.

A method for treating an occlusion within the vasculature of a subjectaccording to any of paragraphs [0009]-[0036], wherein the liquid mediumis any one of iodine-containing contrast medium or gadolinium contrastmedium.

The present disclosure provides a catheter system comprising: a sheathhaving a proximal end and a distal end and a lumen therein; a lasercatheter comprising: a proximal end capable of coupling to a lasergenerator; a distal end; and at least one emitter coupled to the lasergenerator; wherein the catheter is disposed within the sheath, whereuponthe distal end of the laser catheter being disposed proximate the distalend of the sheath, a cavity between the distal end of the laser catheterand the distal end of the sheath is created; a means for introducing aliquid medium into the cavity; a handle comprising: a base coupled tothe proximal end of the sheath; and a drive mechanism translatablycoupled to the base, the drive mechanism coupled to the laser cathetersuch that translation of the drive mechanism relative to the base causestranslation of the laser catheter within the lumen of the sheath.

A catheter system according to any of paragraphs [0009]-[0038], whereinthe drive mechanism comprises: a control element movably coupled to thebase; and a coupling translatably coupled to the base and driven by thecontrol element, the coupling coupled to the laser catheter such thatmovement of the control element relative to the base causes translationof the laser catheter within the lumen of the sheath.

A catheter system according to any of paragraphs [0009]-[0039], whereinthe control element is rotatably coupled to the base, and rotation ofthe control element relative to the base causes translation of the lasercatheter within the lumen of the sheath.

A catheter system according to any of paragraphs [0009]-[0040], whereinthe control element includes a first threaded surface, and the drivemechanism further includes a shaft that is translatable within the baseand coupled to the coupling, the shaft including a second threadedsurface, and the second threaded surface coupling to the first threadedsurface such that rotation of the control element relative to the basecauses translation of the shaft within the base and translation of thelaser catheter within the lumen of the sheath.

A catheter system according to any of paragraphs [0009]-[0041], whereinthe handle further comprises a tube coupled to the base, the tubereceiving the laser catheter, and wherein the shaft includes an innerlumen that translatably receives the tube as the shaft translates withinthe base.

A catheter system according to any of paragraphs [0009]-[0042], whereinthe drive mechanism further comprises a seal coupled to the shaft, theseal translatably engaging the tube.

A catheter system according to any of paragraphs [0009]-[0043], whereinthe tube is a hypotube.

A catheter system according to any of paragraphs [0009]-[004], whereinthe base includes a first key feature, the shaft includes a second keyfeature that couples to the first key feature to inhibit rotation of theshaft relative to the base.

A catheter system according to any of paragraphs [0009]-[0044], whereinthe base includes an opening disposed within the control element, thesecond threaded surface extending through the opening to couple to thefirst threaded surface.

The present disclosure provides a handle for coupling to a sheath and alaser catheter, the handle comprising: a base configured to couple to aproximal end of the sheath; and a drive mechanism translatably coupledto the base, the drive mechanism configured to couple to the lasercatheter such that translation of the drive mechanism relative to thebase causes translation of the laser catheter within a lumen of thesheath.

A handle according to any of paragraphs [0009]-[0047], wherein the drivemechanism comprises: a control element movably coupled to the base; anda coupling translatably coupled to the base and driven by the controlelement, the coupling being configured to couple to the laser cathetersuch that movement of the control element relative to the base causestranslation of the laser catheter within the lumen of the sheath.

A handle according to any of paragraphs [0009]-[0048], wherein thecontrol element is rotatably coupled to the base, and rotation of thecontrol element relative to the base causes translation of the lasercatheter within the lumen of the sheath.

A handle according to any of paragraphs [0009]-[0049], wherein thecontrol element includes a first threaded surface, and the drivemechanism further includes a shaft that is translatable within the baseand coupled to the coupling, the shaft including a second threadedsurface, and the second threaded surface coupling to the first threadedsurface such that rotation of the control element relative to the basecauses translation of the shaft within the base and translation of thelaser catheter within the lumen of the sheath.

A handle according to any of paragraphs [0009]-[0050], wherein thehandle further comprises a tube coupled to the base, the tube receivingthe laser catheter, and wherein the shaft includes an passageway thattranslatably receives the tube as the shaft translates within the base.

A handle according to any of paragraphs [0009]-[0051], wherein the drivemechanism further comprises a seal coupled to the shaft, the sealtranslatably engaging the tube.

A handle according to any of paragraphs [0009]-[0052], wherein the tubeis a hypotube.

A handle according to any of paragraphs [0009]-[0053], wherein the baseincludes a first key feature, the shaft includes a second key featurethat couples to the first key feature to inhibit rotation of the shaftrelative to the base.

A handle according to any of paragraphs [0009]-[0054], wherein the baseincludes an opening disposed within the control element, the secondthreaded surface extending through the opening to couple to the firstthreaded surface.

The present disclosure provides a catheter comprising: an outer sheathhaving a proximal end, a distal end and a porous attenuating memberdisposed adjacent the distal end, wherein the porous attenuating membercomprises a plurality of openings; an inner sheath having a proximal endand a distal end, wherein the inner sheath is disposed radially withinthe outer sheath; and at least one emitter coupled to a laser generator,wherein the at least one emitter is disposed radially within the outersheath such that the at least one emitter is disposed radially withinthe attenuating member.

A catheter according to any of paragraphs [0009]-[0056], wherein theporous attenuating member is constructed to form a semi-rigidbiocompatible structure.

A catheter according to any of paragraphs [0009]-[0057], wherein theporous attenuating member is constructed to form a rigid biocompatiblestructure.

A catheter according to any of paragraphs [0009]-[0058], wherein theouter sheath comprises a non-porous biocompatible layer.

A catheter according to any of paragraphs [0009]-[0059], wherein theporous attenuating member is integrally disposed within the solidbiocompatible layer.

A catheter according to any of paragraphs [0009]-[0060], wherein theporous attenuating member is disposed on the exterior of the solidbiocompatible layer.

A catheter according to any of paragraphs [0009]-[0061], wherein theporous attenuating member is disposed on the interior of the solidbiocompatible layer.

A catheter according to any of paragraphs [0009]-[0062], wherein theporous attenuating member comprises a plurality of openings, wherein theplurality of openings comprise at least one of the following shapes:circle; oval; triangle; square; rectangle; helix; polygon; diamond;pentagon; hexagon; heptagon; octagon; nonagon; and decagon.

A catheter according to any of paragraphs [0009]-[0063], wherein theliquid medium is contrast medium or contrast solution.

A catheter according to any of paragraphs [0009]-[0064], wherein theliquid medium is any one of iodine-containing contrast medium orgadolinium contrast medium.

A catheter according to any of paragraphs [0009]-[0065], wherein theliquid medium is configured to exhibit high absorption of light energyemitted from the at least one emitter at wavelengths of between about 1nanometer to about 1 millimeter, at pulse durations between about 1nanosecond to about 1 second, and at frequencies between about 1 pulseper second to about 500 pulses per second.

A catheter according to any of paragraphs [0009]-[0066], wherein the atleast one emitter is two or more concentric emitters.

A catheter according to any of paragraphs [0009]-[0067], wherein the atleast one emitter is two or more single-fiber emitters.

A catheter according to any of paragraphs [0009]-[0068], wherein the atleast one emitter is configured to translate within the outer sheath.

A catheter according to any of paragraphs [0009]-[0069], wherein thedistal end of the outer sheath comprises an open configuration.

A catheter according to any of paragraphs [0009]-[0070], wherein thedistal end of the outer sheath comprises a closed configuration.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: introducing acatheter within vasculature of a subject, the catheter comprising: anouter sheath having a proximal end, a distal end and a porousattenuating member disposed adjacent the distal end, wherein the porousattenuating member comprises a plurality of openings; an inner sheathhaving a proximal end and a distal end, wherein the inner sheath isdisposed radially within the outer sheath; and at least one emittercoupled to a laser generator, wherein the at least one emitter isdisposed radially within the outer sheath; one or more liquid mediumports coupled to the at least one lumen; positioning the outer sheath ata location such that the porous attenuating member is adjacent anocclusion within the vasculature; positioning the at least one emitterthe such that the at least one emitter is disposed radially within theporous attenuating member; introducing a liquid medium into the outersheath; activating the at least one emitter to transmit pulses of lightenergy into the liquid medium; wherein transmitting the pulses of lightenergy from the emitter into the liquid medium generates at least onepropagating laser-induced pressure waves that pass through the outersheath and the porous attenuating member and disrupt at least a portionof the occlusion.

The present disclosure provides a kit comprising: an outer sheath havinga proximal end, a distal end and a porous attenuating member disposedadjacent the distal end, wherein the porous attenuating member comprisesa plurality of openings; and a laser catheter configured to be disposedwithin the porous attenuating member, the laser catheter comprising: aninner sheath having a proximal end and a distal end, wherein the innersheath is configured to be disposed radially within the outer sheath;and at least one emitter coupled to a laser generator, wherein the atleast one emitter is configured to be disposed radially within the outersheath such that the at least one emitter is disposed radially withinthe porous attenuating member.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: introducing anouter sheath within vasculature of a subject, wherein the outer sheathcomprises a proximal end, a distal end and a porous attenuating memberdisposed adjacent the distal end, wherein the porous attenuating membercomprises a plurality of openings; introducing a laser catheter withinthe vasculature of the subject, wherein the laser catheter is configuredto be disposed within the porous attenuating member, wherein the lasercatheter comprises an inner sheath having a proximal end and a distalend, wherein the inner sheath is configured to be disposed radiallywithin the outer sheath; and at least one emitter coupled to a lasergenerator, wherein the at least one emitter is disposed radially withinthe outer sheath; one or more liquid medium ports coupled to the atleast one lumen; positioning the outer sheath at a location such thatthe porous attenuating member is adjacent a portion of an occlusionwithin the vasculature; positioning the at least one emitter the suchthat the at least one emitter is disposed radially within the porousattenuating member; introducing a liquid medium into the outer sheath;activating the at least one emitter to transmit pulses of light energyinto the liquid medium; wherein transmitting the pulses of light energyfrom the emitter into the liquid medium generates at least onepropagating laser-induced pressure waves that pass through the outersheath and the porous attenuating member and disrupt at least a portionof the occlusion.

A method according to any of paragraphs [0009]-[0074], furthercomprising the step of re-positioning the outer sheath such that theattenuating member is adjacent another portion of the occlusion.

A method according to any of paragraphs [0009]-[0075], furthercomprising the step of re-positioning the laser catheter within outersheath.

A method according to any of paragraphs [0009]-[0076], wherein thewithin the laser catheter is re-positioned within the attenuatingmember.

A method according to any of paragraphs [0009]-[0077], furthercomprising the steps of removing the laser catheter from the vasculatureand removing the outer sheath from the vasculature.

A method according to any of paragraphs [0009]-[0078], furthercomprising the step of inserting a drug-coated balloon into thevasculature such that the drug-coated balloon is disposed adjacent to aremaining portion of the occlusion.

A method according to any of paragraphs [0009]-[0079], furthercomprising the step of inflating the drug-coated balloon and applying adrug disposed on the drug-coated balloon to the remaining portion of theocclusion.

The present disclosure provides a catheter comprising: a sheath having aguidewire lumen, a proximal end, and a distal end; a plurality ofemitters circumferentially arranged around or adjacent to the guidewirelumen, wherein each emitter emits laser light; and means for directinglaser light emitted from the emitter towards the guidewire lumen or aguidewire within the guidewire lumen.

A catheter according to any of paragraphs [0009]-[0081], wherein themeans for directing laser light emitted from the emitter towards theguidewire lumen or a guidewire within the guidewire lumen comprises anouter band coupled to the distal end of the sheath, wherein the outerband comprises a distal end, and the emitter is disposed proximate thedistal end of the outer band.

A catheter according to any of paragraphs [0009]-[0082], wherein theemitter is directed at the guidewire lumen or a guidewire within theguidewire lumen.

A catheter according to any of paragraphs [0009]-[0083], wherein themeans for directing laser light emitted from the emitter towards theguidewire lumen or a guidewire comprises a cap coupled to the distal endof the sheath.

A catheter according to any of paragraphs [0009]-[0084], wherein the capcomprises an interior side and an exterior side, wherein the interiorside is tapered to direct laser-induced pressure wave and/or cavitationevent towards the guidewire lumen or a guidewire within the guidewirelumen resulting in excitation and/or vibration of the guidewire.

A catheter according to any of paragraphs [0009]-[0085], wherein theemitter is disposed proximate the interior side of the cap.

A catheter according to any of paragraphs [0009]-[0086], wherein thesheath is an inner sheath, and further comprising an outer sheathtranslatably receiving the inner sheath.

A catheter according to any of paragraphs [0009]-[0087], wherein theouter sheath comprises a sleeve, and wherein the means for directinglaser light emitted from the emitter towards the guidewire lumen or aguidewire within the guidewire lumen comprises an attenuating member ofthe outer sheath coupled to the sleeve.

A catheter according to any of paragraphs [0009]-[0088], wherein theattenuating member comprises an inner surface, an outer surface, and aplurality of openings extending from the inner surface to the outersurface.

A catheter according to any of paragraphs [0009]-[0088], wherein theattenuating member contains a plurality of openings which comprise atleast one of the following shapes: circle; oval; triangle; square;rectangle; helix; polygon; diamond; pentagon; hexagon; heptagon;octagon; nonagon; and decagon.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: positioning acatheter within the vasculature of the subject, the catheter comprising:a sheath having a guidewire lumen, a proximal end, and a distal end; aplurality of emitters circumferentially arranged around or adjacent tothe guidewire lumen, wherein emitter is capable of emitting laser light;means for directing laser light emitted from the emitter towards theguidewire lumen or a guidewire within the guidewire lumen; positioningthe distal end of the sheath adjacent the occlusion within thevasculature; delivering a liquid medium to the distal end of the sheath;activating the emitter to transmit pulses of light energy through theliquid medium; wherein transmitting the pulses of light energy from theemitter into the liquid medium generates a plurality of propagatinglaser-induced pressure waves that disrupt at least a portion of theocclusion; and wherein the means for directing laser light emitted fromthe emitter towards the guidewire lumen or a guidewire within theguidewire lumen induces vibrations within the guidewire.

A method according to any of paragraphs [0009]-[0091], wherein the meansfor directing laser light emitted from the emitter towards the guidewirelumen or a guidewire within the guidewire lumen comprises an outer bandcoupled to the distal end of the sheath, wherein the outer bandcomprises a distal end, and the emitter is disposed proximate the distalend of the outer band.

A method according to any of paragraphs [0009]-[0092], wherein the meansfor directing laser light emitted from the emitter towards the guidewirelumen or a guidewire within the guidewire lumen comprises an outer bandcoupled to the distal end of the sheath, wherein the outer bandcomprises a distal end, and the emitter is disposed proximate the distalend of the outer band.

A method according to any of paragraphs [0009]-[0093], wherein theemitter is directed at the guidewire lumen or a guidewire in theguidewire lumen.

A method according to any of paragraphs [0009]-[0094], wherein the meansfor directing laser light emitted from the emitter towards the guidewirelumen or a guidewire comprises a cap coupled to the distal end of thesheath.

A method according to any of paragraphs [0009]-[0095], wherein the capcomprises an interior side and an exterior side, wherein the interiorside is tapered to direct a laser-induced pressure wave and/orcavitation event towards the guidewire lumen or a guidewire within theguidewire lumen resulting in excitation and/or vibration of theguidewire.

A method according to any of paragraphs [0009]-[0096], wherein theemitter is disposed proximate the interior side of the cap.

A method according to any of paragraphs [0009]-[0097], wherein thesheath is an inner sheath, and wherein the catheter further comprises anouter sheath translatably receiving the inner sheath.

A method according to any of paragraphs [0009]-[0098], wherein the outersheath comprises a sleeve, and wherein the means for directing laserlight emitted from the emitter towards the guidewire lumen or aguidewire within the guidewire lumen comprises a attenuating member ofthe outer sheath coupled to the sleeve.

A method according to any of paragraphs [0009]-[0099], wherein theattenuating member comprises an inner surface, an outer surface, and aplurality of openings extending from the inner surface to the outersurface, and wherein transmitting the pulses of light energy from theemitter into the liquid medium generates a plurality of propagatinglaser-induced pressure waves that pass through the plurality ofopenings.

A method according to any of paragraphs [0009]-[0100], wherein theattenuating member contains a plurality of openings which comprise atleast one of the following shapes: circle; oval; triangle; square;rectangle; helix; polygon; diamond; pentagon; hexagon; heptagon;octagon; nonagon; and decagon.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: positioning acatheter within the vasculature of the subject, the catheter comprising:a sheath having a guidewire lumen, a proximal end, and a distal end; aplurality of emitters circumferentially arranged around or adjacent tothe guidewire lumen, wherein emitter is capable of emitting laser light;positioning the distal end of the sheath adjacent the occlusion withinthe vasculature; delivering a liquid medium to the distal end of thesheath; activating the emitter to transmit pulses of light energythrough the liquid medium; wherein transmitting the pulses of lightenergy from the emitter into the liquid medium generates a plurality ofpropagating laser-induced pressure waves that disrupt at least a portionof the occlusion; and wherein the plurality of propagating laser inducedpressure waves induce vibrations within the guidewire.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: positioning acatheter within vasculature of a subject, the catheter comprising: anouter sheath having a proximal end and a distal end; a tip coupled tothe distal end of the outer sheath; an inner sheath having a firstguidewire lumen, a proximal end, and a distal end, wherein the innersheath is disposed radially within the outer sheath, wherein the distalend of the inner sheath is disposed proximate the tip, thereby creatinga cavity among the outer sheath, inner sheath and tip; a sealable valvecoupled to the outer sheath, the sealable valve having a secondguidewire lumen and a seal; one or more emitters disposed within theinner sheath extending from the proximal end of the inner sheath to thedistal end of the inner sheath and into the cavity, wherein the one ormore emitters is coupled to an energy source, such as a laser generator;wherein at least one emitter is disposed within the cavity; positioningthe tip adjacent an occlusion within the vasculature by advancing thecatheter along a guidewire, wherein the guidewire is received in thefirst guidewire lumen and the second guidewire lumen; introducing aliquid medium into the cavity, wherein the liquid medium actuates theseal within the valve and closes an opening between the valve and theguidewire; and; activating the at least one emitter within the cavity totransmit pulses of light energy into the liquid medium; whereintransmitting the pulses of light energy from the emitter into the liquidmedium generates at least one propagating laser-induced pressure wavesthat cause the tip to engage and disrupt at least a portion of thevascular occlusion.

A method according to any of paragraphs [0009]-[0103], wherein thesealable valve further comprises an exterior wall and a flange disposedradially therein, wherein a gap exists between the exterior wall and theflange, and wherein introducing the liquid medium into the cavityincludes introducing the liquid medium to the gap to actuate the sealwithin the valve and close the opening between the valve and theguidewire.

A method according to any of paragraphs [0009]-[0104], wherein thesealable valve further comprises openings within the exterior wallextending into the gap, and wherein introducing the liquid medium to thegap includes introducing the liquid medium to the gap via the openings.

A method according to any of paragraphs [0009]-[0105], wherein theflange is tapered radially inward towards the second guidewire lumen asthe flange progresses from a distal portion of the valve toward aproximal portion of the valve.

The present disclosure provides a catheter comprising a sheath having aproximal end and a distal end; a tip coupled to and forming a cavity atthe distal end of the sheath; one or more emitters carried by the sheathand coupled to an energy source, such as a laser generator, wherein theat least one emitter is disposed within the cavity; and a lightabsorbing material coupled to at least part of the sheath and the tipand disposed such that light emitted from the at least one emitterintersects with the light absorbing material.

A catheter according to any of paragraphs [0009]-[0107], wherein thelight absorbing material is disposed within the cavity.

A catheter according to any of paragraphs [0009]-[0108], wherein thelight absorbing material is disposed outside of the cavity.

A catheter according to any of paragraphs [0009]-[0109], wherein thelight absorbing material is applied as a coating to a support structurelocated within the cavity.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising positioning acatheter within vasculature of a subject, the catheter comprising asheath having a proximal end and a distal end; a tip coupled to andforming a cavity at the distal end of the sheath; one or more emitterscarried by the sheath and disposed toward and/or in the cavity, whereinthe one or more emitters is coupled to an energy source, such as a lasergenerator; a light absorbing material coupled to at least part of thesheath and the tip; positioning the tip adjacent an occlusion within thevasculature by advancing the catheter within the vasculature; andactivating the at least one emitter to transmit a pulse of light energysuch that the light energy intersects with at least a portion of thelight absorbing material.

A method according to any of paragraphs [0009]-[0111], furthercomprising delivering a liquid medium to the cavity.

A method according to any of paragraphs [0009]-[0111], wherein the tipfurther comprises a flexible membrane carrying the light absorbingmaterial, and activating the at least one emitter to transmit the pulseof light energy such that the light energy intersects with the at leasta portion of the light absorbing material causes deflection of theflexible membrane.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising positioning acatheter within the vasculature of the subject, the catheter comprisinga sheath having a proximal end and a distal end; at least one emittercarried by the sheath, wherein each emitter is capable of emitting laserlight; positioning the distal end of the sheath adjacent the occlusionwithin the vasculature; delivering a gas-saturated liquid medium to thedistal end of the sheath; activating the emitter to transmit pulses oflight energy through the gas-saturated liquid medium; whereintransmitting the pulses of light energy from the emitter into thegas-saturated liquid medium generates at least one propagatinglaser-induced pressure wave that disrupts at least a portion of theocclusion.

A method according to any of paragraphs [0009]-[0114], wherein thegas-saturated liquid medium is any one of iodine-containing contrastmedium or gadolinium contrast medium.

A method according to any of paragraphs [0009]-[0115], wherein thegas-saturated liquid medium comprises a super saturated liquid medium.

The present disclosure provides a method for treating an occlusionwithin vasculature of a subject, the method comprising: positioning acatheter within the vasculature of the subject, the catheter comprising:an outer sheath having a proximal end, a distal end, and a lumentherein; an inner sheath comprising: a proximal end capable of couplingto an energy source, such as a laser generator; a distal end oppositethe proximal end; one or more optical fibers extending from the proximalend of the inner sheath to the distal end of the inner sheath; and atleast one emitter coupled to the one or more optical fibers; positioningthe distal end of the outer sheath adjacent the occlusion within thevasculature; positioning the distal end of the inner sheath proximallyrelative to the distal end of the outer sheath to create a cavitybetween the distal end of the inner sheath and the distal end of theouter sheath; delivering a liquid medium to the cavity; and activatingthe emitter to transmit pulses of light energy through the liquidmedium; wherein transmitting the pulses of light energy from the emitterinto the liquid medium generates at least one propagating laser-inducedpressure waves that disrupt at least a portion of the occlusion.

A method according to any of paragraphs [0009]-[0117], furthercomprising: repositioning the inner sheath within outer sheath afteractivating the emitter; and subsequently activating the emitter totransmit pulses of light energy through the liquid medium; whereintransmitting the pulses of light energy from the emitter into the liquidmedium generates at least one propagating laser-induced pressure wavesthat disrupt at least a portion of the occlusion.

A method according to any of paragraphs [0009]-[0118], furthercomprising traversing the entire occlusion with the inner sheath and theouter sheath after activating the emitter.

A method according to any of paragraphs [0009]-[0119], wherein the innersheath further comprises a guidewire lumen, wherein positioning thecatheter within the vasculature of the subject comprises receiving aguidewire in the guidewire lumen and advancing the inner sheath and theouter sheath along the guidewire, and further comprising traversing theocclusion with the guidewire.

A method according to any of paragraphs [0009]-[0120], furthercomprising traversing the occlusion with the inner sheath and withoutthe outer sheath after activating the emitter.

A method according to any of paragraphs [0009]-[0121], furthercomprising: inserting a drug-coated balloon into the vasculature, afteractivating the emitter, such that the drug-coated balloon is disposedadjacent a remaining portion of the occlusion; and inflating thedrug-coated balloon and applying a drug disposed on the drug-coatedballoon to the occlusion.

A catheter, kit and/or method according to any of paragraphs[0009]-[0122], wherein the total energy output for the at least oneemitter is between about 20 to about 1000 millijoules per millimetersquared (mJ/mm²).

A catheter, kit and/or method according to any of paragraphs[0009]-[0123], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of between about 150 nanometers toabout 400 nanometers, at pulse durations between about 1 femtosecond toabout 1 second, and at frequencies between about 1 pulse per second toabout 5000 pulses per second.

A catheter, kit and/or method according to any of paragraphs[0009]-[0124], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of between about 400 nanometers toabout 800 nanometers, at pulse durations between about 1 femtosecond toabout 1 second, and at frequencies between about 1 pulse per second toabout 5000 pulses per second.

A catheter, kit and/or method according to any of paragraphs[0009]-[0125], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of between about 800 nanometers toabout 3,000 nanometers, at pulse durations between about 1 femtosecondto about 1 second, and at frequencies between about 1 pulse per secondto about 5000 pulses per second.

A catheter, kit and/or method according to any of paragraphs[0009]-[0126], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of between about 3,000 nanometers toabout 12,000 nanometers, at pulse durations between about 1 femtosecondto about 1 second, and at frequencies between about 1 pulse per secondto about 5000 pulses per second.

A catheter, kit and/or method according to any of paragraphs[0009]-[0127], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of between about 300 nanometers toabout 360 nanometers, at pulse durations between about 1 femtosecond toabout 1 second, and at frequencies between about 1 pulse per second toabout 5000 pulses per second.

A catheter, kit and/or method according to any of paragraphs[0009]-[0128], wherein the at least one emitter is configured to emitlaser light energy at wavelengths of about 308 nanometers, at pulsedurations between about 10 nanoseconds and about 200 nanoseconds, and atfrequencies between about 1 pulse per second to about 100 pulses persecond.

A catheter, kit and/or method according to any of paragraphs[0009]-[0129], wherein the attenuating member is disposed on theexterior of the outer sheath.

A catheter, kit and/or method according to any of paragraphs[0009]-[0130], wherein the attenuating member is disposed on theinterior of the outer sheath.

A catheter, kit and/or method according to any of paragraphs[0009]-[0131], wherein the attenuating member is disposed integral ofthe outer sheath.

A method for improving the compliance of a blood vessel within asubject, the method comprising locating a calcified portion in the mediaof the blood vessel of the subject, positioning a laser catheter withinthe vasculature of the subject, the catheter comprising a proximal end,a distal end, and at least one emitter disposed at the distal end,positioning a sheath over the laser catheter within the vasculature ofthe subject, wherein the sheath comprises a proximal end, a distal endand a attenuating member disposed adjacent the distal end, positioningthe sheath within the vasculature such that the attenuating member isdisposed adjacent a portion of the calcified portion, positioning thelaser catheter within the vasculature such that the at least one emitteris positioned within the attenuating member and adjacent the portion ofthe calcified portion, introducing a liquid medium into the outer sheathand to the at least one emitter; activating the at least one emitter totransmit pulses of light energy into the liquid medium; emitting one ormore pulses of light energy from the at least one emitter, wherein theone or more pulses of light energy reacts with the liquid medium andgenerates a plurality of propagating laser-induced pressure waves thatdisrupt the calcified portion of the media, thereby improving thecompliance of the blood vessel.

A method according to paragraph [0120] further comprising the step ofre-positioning the sheath such that the attenuating member is adjacentanother calcified portion of the media.

A method according to any of paragraphs [0008]-[0120] further comprisingthe step of re-positioning the laser catheter within sheath.

A method according to any of paragraphs [0008]-[0120], wherein thewithin the laser catheter is re-positioned within the attenuatingmember.

A method according to any of paragraphs [0008]-[0120], furthercomprising the steps of removing the laser catheter from the vasculatureand removing the outer sheath from the vasculature.

A method according to any of paragraphs [0008]-[0016], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 150 nanometers to about 400 nanometers, atpulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

A method according to any of paragraphs [0008]-[0016], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 400 nanometers to about 800 nanometers, atpulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

A method according to any of paragraphs [0008]-[0016], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 800 nanometers to about 3,000 nanometers,at pulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

A method according to any of paragraphs [0009]-[0140], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 3,000 nanometers to about 12,000nanometers, at pulse durations between about 1 femtosecond to about 1second, and at frequencies between about 1 pulse per second to about5000 pulses per second.

A method according to any of paragraphs [0009]-[0141], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of between about 300 nanometers to about 360 nanometers, atpulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

A method according to any of paragraphs [0009]-[0142], wherein the atleast one emitter is configured to emit laser light energy atwavelengths of about 308 nanometers, at pulse durations between about 10nanoseconds and about 200 nanoseconds, and at frequencies between about1 pulse per second to about 100 pulses per second.

A method according to any of paragraphs [0009]-[0143], wherein totalenergy output for the at least one emitter is between about 1 to about100 millijoules per millimeter squared (mJ/mm²).

A method according to any of paragraphs [0009]-[0144], wherein totalenergy output for the at least one emitter is between about 30 to about80 millijoules per millimeter squared (mJ/mm²).

A method according to any of paragraphs [0009]-[0145], wherein theliquid medium is contrast medium or contrast solution.

A method according to any of paragraphs [0009]-[0146], wherein theliquid medium is any one of iodine-containing contrast medium orgadolinium contrast medium.

A method according to any of paragraphs [0009]-[0147], wherein theliquid medium is configured to exhibit high absorption of light energyemitted from the at least one emitter at wavelengths of between about 1nanometer to about 1 millimeter, at pulse durations between about 1nanosecond to about 1 second, and at frequencies between about 1 pulseper second to about 1000 pulses per second.

A method according to any of paragraphs [0009]-[0148], wherein the atleast one emitter is two or more concentric emitters.

A method according to any of paragraphs [0009]-[0149], wherein the atleast one emitter is two or more single-fiber emitters.

A method according to any of paragraphs [0009]-[0150], wherein theattenuating member is constructed to form a semi-rigid biocompatiblestructure.

A method according to any of paragraphs [0009]-[0151], wherein theattenuating member is constructed to form a rigid biocompatiblestructure.

A method according to any of paragraphs [0009]-[0152], wherein thesheath comprises a non-porous biocompatible layer.

A method according to any of paragraphs [0009]-[0153], wherein theattenuating member comprises an inner surface, an outer surface, and aplurality of openings extending from the inner surface to the outersurface.

A method according to any of paragraphs [0009]-[0154], wherein theattenuating member contains a plurality of openings which comprise atleast one of the following shapes: circle; oval; triangle; square;rectangle; helix; polygon; diamond; pentagon; hexagon; heptagon;octagon; nonagon; and decagon.

A method according to any of paragraphs [0009]-[0155], wherein theattenuating member is integrally disposed within the sheath.

A method according to any of paragraphs [0009]-[0156], wherein theattenuating member is disposed on the exterior of the sheath.

A method according to any of paragraphs [0009]-[0157], wherein theattenuating member is disposed on the interior of the sheath.

A method according to any of paragraphs [0009]-[0158], wherein theliquid medium is any one of iodine-containing contrast medium orgadolinium contrast medium.

A method according to any of paragraphs [0009]-[0159], wherein thedistal end of the sheath comprises an open configuration.

A method according to any of paragraphs [0009]-[0160], wherein thedistal end of the sheath comprises a closed configuration.

According to the present disclosure, after penetrating the calcifiedand/or fibrous total occlusion and disrupting at least a portion of theocclusion with the laser-induced pressure wave emitting catheter sheath,the method may also include delivering via a balloon catheter, one ormore therapeutic agents, which is/are disposed on the balloon, whereinthe therapeutic agents may comprise one or more oxidation-insensitivedrugs in a polymer-free drug preparation, including one or more oftaxanes, thalidomide, statins, corticoids, and lipophilic derivatives ofcorticoids. The therapeutic agents may also include one or morelipophilic antioxidants, such as nordihydroguaiaretic acid, resveratroland propyl gallate in a polymer-free preparation. For example, U.S.application Ser. No. 13/628,608, which is a continuation ofInternational Application No. PCT/EP2010/066754, filed Nov. 3, 2010,both of which are hereby incorporated herein by reference in theirentireties for all that they teach and for all purposes, discloses ascoring or cutting balloon catheter providing improved adherence oftherapeutic agents to the balloon catheter using a combination of anoxidation-insensitive drug and a lipophilic antioxidant.

Additionally, U.S. application Ser. No. 13/707,401, filed Dec. 6, 2012,and issued on Oct. 21, 2014, which is a divisional application of U.S.application Ser. No. 11/411,635, filed Apr. 26, 2006, and which claimspriority to U.S. Provisional Application Ser. No. 60/680,450, filed May11, 2005, all of which are hereby incorporated herein by reference intheir entireties for all that they teach and for all purposes, disclosesscoring elements of a balloon catheter coated with a polymer matrix todeliver hydrophobic and lipophilic drugs to regions within a thrombus orplaque.

Additionally, U.S. application Ser. No. 13/310,320, filed Dec. 2, 2011,and issued Oct. 22, 2013, which is a divisional application of U.S.application Ser. No. 12/712,134, filed Feb. 24, 2010, and issued Mar. 6,2012, and U.S. application Ser. No. 12/726,101, filed Mar. 17, 2010, andissued Feb. 14, 2012, which is a continuation-in-part of U.S.application Ser. No. 12/712,134, filed Feb. 24, 2010, and issued Mar. 6,2012, which is a continuation-in-part of U.S. application Ser. No.12/558,420, filed Sep. 11, 2009, which is a continuation-in-part of U.S.application Ser. No. 12/210,344, filed Sep. 15, 2008, and issued Sep. 4,2012, and U.S. application Ser. No. 14/149,862, filed Jan. 8, 2014,which is a continuation of U.S. application Ser. No. 13/560,538, filedJun. 27, 2012, and issued Mar. 18, 2014, which is a divisionalapplication of U.S. application Ser. No. 12/210,344, filed Sep. 15,2008, and issued Sep. 4, 2012, all of which are hereby incorporatedherein by reference in their entireties for all that they teach and forall purposes, disclose methods and devices for local delivery ofwater-soluble and water-insoluble therapeutic agents to the surface ofnormal and diseased body lumens.

Additionally, U.S. application Ser. No. 13/926,515, filed Jun. 25, 2013,which claims priority to U.S. Provisional Application Ser. No.61/665,758, filed Jun. 28, 2012, both of which are hereby incorporatedherein by reference in their entireties for all that they teach and forall purposes, disclose methods and devices for coating a medical devicethat includes a therapeutic agent dispersed in a polymer or oligomermatrix.

The present disclosure also provides a catheter system comprising asheath having a proximal end and a distal end and a lumen therein, alaser catheter comprising, a proximal end, a distal end capable ofcoupling to an energy source, such as a laser generator, and at leastone emitter disposed at the distal end of the laser catheter and coupledto an energy source, such as a laser generator, wherein the catheter isconfigured to be disposed within the sheath, whereupon the distal end ofthe laser catheter being disposed proximate the distal end of thesheath, a cavity between the distal end of the laser catheter and thedistal end of the sheath is created, and a means for introducing aliquid medium into the cavity.

The present disclosure also provides A method for improving thecompliance of a blood vessel within a subject, the method comprisinglocating a calcified portion in the media of the blood vessel of thesubject, positioning a laser catheter within the vasculature of thesubject, the catheter comprising a proximal end, a distal end, and atleast one emitter disposed adjacent the distal end, positioning a sheathover the laser catheter within the vasculature of the subject, whereinthe sheath comprises a proximal end, a distal end and an attenuatingmember disposed at or adjacent the distal end of the sheath, wherein theattenuating member comprises an open area between 40 percent and 60percent, wherein the attenuating member is formed from at least one coilhaving between 75 and 125 wraps per inch, positioning the sheath withinthe vasculature such that the attenuating member is disposed adjacent aportion of the calcified portion in the media of the blood vessel,positioning the laser catheter within the vasculature such that the atleast one emitter is positioned within the attenuating member andadjacent the portion of the calcified portion in the media of the bloodvessel, introducing a liquid medium into the sheath and to the at leastone emitter, and emitting a plurality of pulses of light energy from theat least one emitter into the liquid medium, wherein the plurality ofpulses of light energy react with the liquid medium and generate aplurality of propagating laser-induced pressure waves that disrupt thecalcified portion of media, thereby improving the compliance of theblood vessel.

A method according to paragraph [0167], wherein the at least one coilcomprises a flat wire.

A method according to any of paragraphs [0167]-[0168], wherein the flatwire comprises a height between 0.0005 and 0.002 inches and a width ofbetween 0.002 and 0.010 inches.

A method according to any of paragraphs [0167]-[0169], wherein the flatwire comprises a height of about 0.001 inches and a width of about 0.005inches.

A method according to any of paragraphs [0167]-[0170], wherein a spacingbetween each wrap of flat wire in the coil is between 0.003 and 0.008inches.

A method according to any of paragraphs [0167]-[0171], wherein the coilhas between 90 and 100 wraps per inch.

A method according to any of paragraphs [0167]-[0172], wherein the coilhas about 95 wraps per inch.

A method according to any of paragraphs [0167]-[0173], wherein thesheath comprises a tip and a lumen, wherein the lumen comprises a firstinternal diameter and a second internal diameter proximate the tip,wherein the first internal diameter is smaller than the second internaldiameter.

A method according to any of paragraphs [0167]-[0174], wherein lasercatheter has an outer diameter that is about equal to the first innerdiameter of the tip.

A method according to any of paragraphs [0167]-[0175], wherein a firstdifference between the outer diameter of the laser catheter and thefirst inner diameter of the tip is about 0.0005 inches.

A method according to any of paragraphs [0167]-[0177], wherein a seconddifference between the outer diameter of the laser catheter and thesecond inner diameter of the sheath is about 0.0025 inches.

A method according to any of paragraphs [0167]-[0178], wherein thesheath comprises a tip having a proximal end and a distal end, whereinthe tip tapers from the proximal end to the distal end.

The present disclosure also provides a method for performing anatherectomy within a subject having a vasculature occlusion within thesubject's vasculature, the method comprising inserting a guidewirethrough a vascular occlusion within the vasculature, introducing a lasercatheter into the vasculature and over the guidewire, wherein the lasercatheter comprises at least one emitter, ablating at least a portion ofthe vascular occlusion with the laser catheter, introducing a sheathinto the vasculature and over the laser catheter, wherein the sheathcomprises a distal portion and an attenuating member disposed at oradjacent the distal portion of the sheath, wherein the attenuatingmember comprises an open area between 40 percent and 60 percent, whereinthe attenuating member is formed from at least one coil having between75 and 125 wraps per inch, positioning the sheath within the vasculaturesuch that the attenuating member is disposed radially adjacent acalcified portion within the vasculature, positioning the laser catheterwithin the vasculature such that the at least one emitter is positionedwithin the attenuating member and radially adjacent the calcifiedportion, introducing a liquid medium into the sheath and to the at leastone emitter; and emitting a plurality of pulses of light energy from theat least one emitter into the liquid medium, wherein the plurality ofpulses of light energy react with the liquid medium and generate aplurality of propagating laser-induced pressure waves that disrupt thecalcified portion.

A method according to paragraph [0179] further comprising extending thelaser catheter distally of the sheath and ablating another portion of asecond vascular occlusion, positioning the sheath within the vasculaturesuch that the attenuating member is disposed radially adjacent a secondcalcified portion of the second vascular occlusion, positioning thelaser catheter within the vasculature such that the at least one emitteris positioned within the attenuating member and radially adjacent thesecond calcified portion, introducing a liquid medium into the sheathand to the at least one emitter, and emitting a plurality of pulses oflight energy from the at least one emitter into the liquid medium,wherein the plurality of pulses of light energy react with the liquidmedium and generate a plurality of propagating laser-induced pressurewaves that disrupt the second calcified portion.

The present disclosure also provides a catheter system comprising alaser catheter comprising a proximal end, a distal end, and at least oneemitter disposed adjacent the distal end, a sheath configured to bedisposed over the laser catheter and configured to receive a liquidmedium, the sheath comprising a proximal end, a distal end, and anattenuating member disposed at or adjacent the distal end of the sheath,wherein the attenuating member comprises an open area between 40 percentand 60 percent, wherein the attenuating member is formed from at leastone coil having between 75 and 125 wraps per inch.

A system according to paragraph [0181], wherein the at least one coilcomprises a flat wire.

A system according to any of paragraphs [0181]-[0182], wherein the flatwire comprises a height between 0.0005 and 0.002 inches and a width ofbetween 0.002 and 0.010 inches.

A system according to any of paragraphs [0181]-[0183], wherein a spacingbetween each wrap of flat wire in the coil is between 0.003 and 0.008inches.

A system according to any of paragraphs [0181]-[0184], wherein the atleast one coil has between 90 and 100 wraps per inch.

A system according to any of paragraphs [0181]-[0185], wherein thesheath further comprises an inner liner, an outer jacket; and anintermediate layer disposed concentrically between the inner liner andthe outer jacket.

A system according to any of paragraphs [0181]-[0186], wherein thebraided structure is integrally disposed within the inner liner or theouter jacket.

A system according to any of paragraphs [0181]-[0187], wherein thebraided structure is integrally disposed within the inner liner.

A system according to any of paragraphs [0181]-[0188], wherein thebraided structure is integrally disposed within the outer jacket.

A system according to any of paragraphs [0181]-[0188], wherein thebraided structure is integrally disposed within the outer jacket and theinner liner.

The present disclosure also provides a catheter system comprising alaser catheter comprising a proximal end, a distal end, and at least oneemitter disposed adjacent the distal end, a sheath configured to bedisposed over the laser catheter and configured to receive a liquidmedium, the sheath comprising a proximal end, a distal end, and anattenuating member disposed at or adjacent the distal end of the sheath,wherein the attenuating member comprises a braided structure having abraid density between 40 and 80 picks per inch.

A system according to paragraph [0191], wherein the braided structurehas an open area between 55 percent and 75 percent.

A system according to any of paragraphs [0191]-[0192], wherein thebraided structure has between 12 and 20 carriers.

A system according to any of paragraphs [0191]-[0193], wherein thesheath further comprises an inner liner, an outer jacket, and anintermediate layer disposed concentrically between the inner liner andthe outer jacket.

A system according to any of paragraphs [0191]-[0194], wherein thebraided structure is integrally disposed within the inner liner or theouter jacket.

A system according to any of paragraphs [0191]-[0195], wherein thebraided structure is integrally disposed within the inner liner.

A system according to any of paragraphs [0191]-[0196], wherein thebraided structure is integrally disposed within the outer jacket.

A system according to any of paragraphs [0191]-[0197], wherein thebraided structure is integrally disposed within the outer jacket and theinner liner.

The present disclosure also provides a system comprising: a sheathhaving a proximal end and a distal end and a lumen therein, the lumenbeing configured to translatably receive a device having a distal end; ahandle coupled to the sheath; and a treatment mode selection systemcoupled to the handle, the treatment mode selection system comprising auser input being actuatable to configure the device from a firstconfiguration to a second configuration and vice versa, in the firstconfiguration the distal end of the device being disposed distally fromthe distal end of the sheath, and in the second configuration the distalend of the device being disposed proximally from the distal end of thesheath and within the lumen.

A system according to paragraph [0198], wherein the user input comprisesa translatable button.

A system according to paragraph [0198], wherein the user input comprisesa rotatable component.

The present disclosure also provides a laser catheter system,comprising: a sheath having a proximal end and a distal end and a lumentherein; a laser catheter translatably disposed within the sheath, thelaser catheter comprising: a proximal end configured to couple to alaser generator; a distal end; at least one emitter configured to coupleto the laser generator; a handle coupled to the sheath and translatablycoupled to the laser catheter; a treatment mode selection system coupledto the sheath, the treatment mode selection system comprising a userinput being actuatable to configure the laser catheter system from afirst configuration to a second configuration and vice versa, in thefirst configuration the distal end of the laser catheter being disposeddistally from the distal end of the sheath, and in the secondconfiguration the distal end of the laser catheter being disposedproximally from the distal end of the sheath and within the lumen andthereby creating a cavity between the distal end of the laser catheterand the distal end of the sheath.

A system according to paragraph [0201], wherein the user input isactuatable to configure at least one operating parameter of the lasergenerator.

As used herein, “at least one,” “one or more,” and “and/or” areopen-ended expressions that are both conjunctive and disjunctive inoperation. For example, each of the expressions “at least one of A, Band C,” “at least one of A, B, or C,” “one or more of A, B, and C,” “oneor more of A, B, or C,” and “A, B, and/or C” means A alone, B alone, Calone, A and B together, A and C together, B and C together, or A, B andC together. When each one of A, B, and C in the above expressions refersto an element, such as X, Y, and Z, or class of elements, such asX₁-X_(n), Y₁-Y_(m), and Z₁-Z_(o), the phrase is intended to refer to asingle element selected from X, Y, and Z, a combination of elementsselected from the same class (for example, X₁ and X₂) as well as acombination of elements selected from two or more classes (for example,Y₁ and Z_(o)).

It is to be noted that the term “a” or “an” entity refers to one or moreof that entity. As such, the terms “a” (or “an”), “one or more” and “atleast one” can be used interchangeably herein. It is also to be notedthat the terms “comprising,” “including,” and “having” can be usedinterchangeably.

The term “about” when used in conjunction with a numeric value shallmean plus and/or minus ten percent (10%) of that numeric value, unlessotherwise specifically mentioned herein.

The term “attenuating member” as used herein is any component whichalters a cavitation event, and/or vapor bubble. An example of anattenuating member is an element which minimally affects the laserinduced pressure wave, yet alters the cavitation event and/or the vaporbubble. An example of an attenuating member is a porous attenuatingmember. The attenuating member, however, does not need to be porous andmay include a solid configuration.

The term “catheter” as used herein generally refers to a tube that canbe inserted into a body cavity, duct, lumen, or vessel, such as thevasculature system. In most uses, a catheter is a relatively thin,flexible tube (“soft” catheter), though in some uses, it may be alarger, solid-less flexible—but possibly still flexible—catheter (“hard”catheter). In some uses a catheter may contain a lumen along part or allof its length to allow the introduction of other catheters orguidewires. An example of a catheter is a sheath.

The term “balloon catheter” as used herein generally refers to thevarious types of catheters which carry a balloon for containing fluids.Balloon catheters may also be of a wide variety of inner structure, suchas different lumen design, of which there are at least three basictypes: triple lumen, dual lumen and co-axial lumen. All varieties ofinternal structure and design variation are meant to be included by useof the term “balloon catheter” herein. In some uses, balloon catheterscan be used to perform angioplasty.

The term “cavitation event” as used herein describes the rapid fluidmovement that leads to collapse of a vapor bubble to its smallestradius. In some cases, a cavitation event may include the generation ofa pressure wave.

The terms “coupler” or “fiber optic coupler” refers to the optical fiberdevice with one or more input fibers or emitters and one or severaloutput fibers or emitters. Fiber couplers are commonly special opticalfiber devices with one or more input fibers or emitters for couplingthese fibers or emitters to an energy source. The energy source can beanother optical energy carrying fiber or emitter which is coupled to oneor more additional fibers or emitters.

The term “emitter” as used herein refers to a fiber or an opticalcomponent (including any portion thereof, such as the end of a fiber)that emits light from a distal end of device, such as a catheter,towards a desired target. In some uses, this target can be tissue, or anabsorptive media, such as contrast fluid. An emitter can be the outputend of any device that transports light from an optical energy source toa target or treatment area. These optical energy transport devices caninclude glass or fused silica fiber optics, plastic fiber optics, air orgas light guides, and liquid light guides. As described herein, anemitter or emitters can be used to emit light of any wavelength. Anemitter or emitters can emit light, including but not limited to, laserlight, white light, visible light, infrared light, and ultravioletlight.

According to the present disclosure, the catheter contains at least oneemitter, which may comprise glass or fused silica fiber optics, plasticfiber optics, air or gas light guides, and liquid light guides. Examplesof a liquid light guide, or a catheter that contain a liquid light guidecan be seen in U.S. application Ser. No. 11/923,488, filed Oct. 24, 2007and U.S. application Ser. No. 12/254,254, filed Oct. 20, 2008, both ofwhich are hereby incorporated herein by reference in their entiretiesfor all that they teach and for all purposes.

The term “flexible structure” as used herein shall mean a structure thatis able to bend or otherwise conform to the shape of the vasculature asit passes therethrough. The term “radial flexible structure” shallinclude a flexible structure that is also able to expand and/or contractin the radial direction upon a laser induced pressure wave passingtherethrough.

A “laser emitter” as used herein refers to an end portion of a fiber oran optical component that emits laser light from a distal end of thecatheter towards a desired target. In some uses, this target can betissue, or an absorptive media, such as contrast fluid.

The term “laser-induced pressure wave” as used herein is a pressure wavecaused by a reaction between laser light and an absorptive material. Thelaser-induced pressure wave may be generated in a gas, liquid (e.g.,saline that may or may not include a contrast medium) or solid.

The term “means” as used herein shall be given its broadest possibleinterpretation in accordance with 35 U.S.C. § 112(f). Accordingly, aclaim incorporating the term “means” shall cover all structures,materials, or acts set forth herein, and all of the equivalents thereof.Further, the structures, materials or acts and the equivalents thereofshall include all those described in the summary, brief description ofthe drawings, detailed description, abstract, and claims themselves.

The term an “optical fiber” (or laser active fibre) as used hereinrefers to a flexible, transparent fiber made of an opticallytransmissive material, such as glass (silica) or plastic, whichfunctions as a waveguide, or “light pipe”, to transmit light between thetwo ends of the fiber.

The term “porous attenuating member” as used herein shall mean anattenuating member constructed of a rigid member or semi-rigid memberhaving openings therein. Examples of a rigid member and a semi-rigidmember include a member constructed of coils, braids, laser-cut tubing,reinforced polymer extrusions, patterned plastics, metals and ceramics.Specific materials used to construct such rigid member and a semi-rigidmember may include nitinol (which is a nickel-titanium alloy), stainlesssteel, titanium, silver, aluminum, cobalt, chromium, pebax, silicone,urethane, polyethylene and derivatives, nylons, polytetrafluoroethyleneand derivatives, polyethylene terephthalate, polypropylene, poly(etherether ketone), hydroxyapatite, alumina, tricalcium phosphate, silicatesor other biocompatible metals, ceramics or polymers. Possibleconfigurations for the porous attenuating member include, but are notlimited to, spiral cuts, interrupted spiral cut, honeycomb, latticestructures as found commonly in vascular stents, slots, offset slots,helices, slits that are either longitudinal, radial, circumferential, ora combination thereof, openings that are shaped cutouts. The scope ofthis disclosure also encompasses the “porous attenuating member” beingconstructed of a flexible structure and/or a radial flexible structure,although it may be preferable for the attenuating to be constructed of arigid member or semi-rigid member.

The term “rigid structure” as used herein shall mean a structure that isable to bend or otherwise conform to the shape of the vasculature as itpasses therethrough but is substantially unable to expand and/orcontract in the radial direction upon a laser induced pressure wavepassing therethrough.

The term “semi-rigid structure” as used herein shall mean a structurethat is partly rigid with an additional degree of flexibility as itpasses through the vasculature but is substantially unable to expandand/or contract in the radial direction upon a laser induced pressurewave passing therethrough.

The term “sheath” as used herein generally refers to a tube that can beinserted into a body cavity duct, lumen, or vessel, such as thevasculature system that allows for the introduction of catheters and theintroduction of fluid along its length. An example of a catheter thatcan be introduced into a sheath is a laser catheter. An example of fluidthat can be introduced into a sheath is an absorptive fluid such ascontrast. The sheath can have a closed end or an open end. Because thesheath is a tube that can be inserted into a body cavity, duct, lumen,or vessel, such as the vasculature system, the sheath may also beconsidered a catheter. Accordingly, a catheter, such as a lasercatheter, can be introduced into another catheter.

The term “therapeutic agent” as used herein generally refers to anyknown or hereafter discovered pharmacologically active agent thatprovides therapy to a subject through the alleviation of one or more ofthe subject's physiological symptoms. A therapeutic agent may be acompound that occurs in nature, a chemically modified naturallyoccurring compound, or a compound that is chemically synthesized. Theagent will typically be chosen from the generally recognized classes ofpharmacologically active agents, including, but not necessarily limitedto, the following: analgesic agents; anesthetic agents; antiarthriticagents; respiratory drugs, including antiasthmatic agents; anticanceragents, including antineoplastic drugs; anticholinergics;anticonvulsants; antidepressants; antidiabetic agents; antidiarrheals;antihelminthics; antihistamines; antihyperlipidemic agents;antihypertensive agents; anti-infective agents such as antibiotics andantiviral agents; antiinflammatory agents; antimigraine preparations;antinauseants; antiparkinsonism drugs; antipruritics; antipsychotics;antipyretics; antispasmodics; antitubercular agents; antiulcer agents;antiviral agents; anxiolytics; appetite suppressants; attention deficitdisorder (ADD) and attention deficit hyperactivity disorder (ADHD)drugs; cardiovascular preparations including calcium channel blockers,CNS agents; beta-blockers and antiarrhythmic agents; central nervoussystem stimulants; cough and cold preparations, including decongestants;diuretics; genetic materials; herbal remedies; hormonolytics; hypnotics;hypoglycemic agents; immunosuppressive agents; leukotriene inhibitors;mitotic inhibitors; restenosis inhibitors; muscle relaxants; narcoticantagonists; nicotine; nutritional agents, such as vitamins, essentialamino acids and fatty acids; ophthalmic drugs such as antiglaucomaagents; parasympatholytics; psychostimulants; sedatives; steroids;sympathomimetics; tranquilizers; and vasodilators including generalcoronary, peripheral and cerebral.

The term “vapor bubble” as used herein is a gaseous cavity createdwithin a liquid.

The terms “vasculature” and “vascular” as used herein refer to any partof the circulatory system of a subject, including peripheral andnon-peripheral arteries and veins. Vasculature can be comprised ofmaterials such as nucleic acids, amino acids, carbohydrates,polysaccharides, lipids fibrous tissue, calcium deposits, remnants ofdead cells, cellular debris and the like.

The term “vascular occlusion” or “occlusion” refers to buildup of fats,lipids, fibrin, fibro-calcific plaque, thrombus and otheratherosclerotic tissue within the lumen or within the intima of anartery that either narrows or completely obstructs the inner lumen theartery thereby restricting or blocking normal blood flow through theartery segment. The occlusion may be partially or totally occlude thevasculature. Accordingly, the term “vascular occlusion” or “occlusion”shall include both a total occlusion and a partial occlusion.Alternatively, a vascular occlusion or occlusion may also be referred toas a vascular obstruction (or obstruction) or a vascular restriction (orrestriction). A vascular obstruction may, therefore, be referred to as atotal obstruction or a partial obstruction, and a vascular restrictionmay be referred to as a total restriction or a partial restriction.

It should be understood that every maximum numerical limitation giventhroughout this disclosure is deemed to include each and every lowernumerical limitation as an alternative, as if such lower numericallimitations were expressly written herein. Every minimum numericallimitation given throughout this disclosure is deemed to include eachand every higher numerical limitation as an alternative, as if suchhigher numerical limitations were expressly written herein. Everynumerical range given throughout this disclosure is deemed to includeeach and every narrower numerical range that falls within such broadernumerical range, as if such narrower numerical ranges were all expresslywritten herein.

The preceding is a simplified summary of the disclosure to provide anunderstanding of some aspects of the disclosure. This summary is neitheran extensive nor exhaustive overview of the disclosure and its variousaspects, embodiments, and configurations. It is intended neither toidentify key or critical elements of the disclosure nor to delineate thescope of the disclosure but to present selected concepts of thedisclosure in a simplified form as an introduction to the more detaileddescription presented below. As will be appreciated, other aspects,embodiments, and configurations of the disclosure are possibleutilizing, alone or in combination, one or more of the features setforth above or described in detail below.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings are incorporated into and form a part of thespecification to illustrate several examples of the present disclosure.These drawings, together with the description, explain the principles ofthe disclosure. The drawings simply illustrate preferred and alternativeexamples of how the disclosure can be made and used and are not to beconstrued as limiting the disclosure to only the illustrated anddescribed examples. Further features and advantages will become apparentfrom the following, more detailed, description of the various aspects,embodiments, and configurations of the disclosure, as illustrated by thedrawings referenced below.

FIG. 1 illustrates an exemplary ablation system, including a lasergenerator and a laser induced pressure wave emitting catheter sheath;

FIG. 2A is a schematic view of a distal portion of the laser inducedpressure wave emitting catheter sheath of FIG. 1, according to oneembodiment of the present disclosure;

FIG. 2B is an elevation view of an embodiment of the distal portion ofthe laser induced pressure wave emitting catheter, according to oneembodiment of the present disclosure;

FIG. 2C is a cross-sectional view (through plane C in FIG. 2B) of thedistal portion of the laser induced pressure wave emitting catheter;

FIG. 2B′ is an elevation view of an embodiment of the distal portion ofthe laser induced pressure wave emitting catheter, according to oneembodiment of the present disclosure;

FIG. 2C′ is a cross-sectional view (through plane C in FIG. 2B′) of thedistal portion of the laser induced pressure wave emitting catheter,according to one embodiment of the present disclosure;

FIG. 2D is a cross-sectional view (through plane D in FIG. 2C) of thedistal portion of the laser induced pressure wave emitting catheter,according to one embodiment of the present disclosure;

FIG. 3 is a cross-sectional view of the distal portion of the laserinduced pressure wave emitting catheter, according to one embodiment ofthe present disclosure;

FIG. 4 is a cross-sectional view of the distal portion of the laserinduced pressure wave emitting catheter, according to one embodiment ofthe present disclosure;

FIG. 5 is a perspective view of an embodiment of the distal portion ofthe laser induced pressure wave emitting catheter, according to oneembodiment of the present disclosure;

FIG. 5A is a cross-sectional view (through plane A in FIG. 5) of thedistal portion of the laser induced pressure wave emitting catheter,according to one embodiment of the present disclosure;

FIG. 5A′ is a cross-sectional view (through plane A in FIG. 5) of thedistal portion of the laser induced pressure wave emitting catheter,according to one embodiment of the present disclosure;

FIG. 6 is a partially transparent elevation view of the distal portionof a laser catheter disposed at one location within the distal portionof a catheter sheath;

FIG. 6A is a partially transparent elevation view of the distal portionof the laser catheter disposed at an alternative location within thedistal portion of the catheter sheath, in comparison to the position ofthe laser catheter in FIG. 6;

FIG. 6B is an enlarged partial perspective view of the distal portion ofan alternative laser catheter including a deflector coupled to thedistal end of the laser catheter;

FIG. 7 is a perspective view of a laser catheter including a shield ordeflector as the distal end thereof, according to one embodiment of thepresent disclosure, wherein the laser catheter is disposed at onelocation within the distal portion of a catheter sheath;

FIG. 8 is an elevation view of a removable tip for an ablation catheter,according to one embodiment of the present disclosure;

FIG. 8A is a cross-sectional view (through plane A in FIG. 8) of aremovable tip for an ablation catheter;

FIG. 9 is a representative flow diagram of a method of treating asubject using a catheter, according to one embodiment of the presentdisclosure;

FIG. 10 is a perspective view of a laser catheter and a guidewire,according to one embodiment of the present disclosure;

FIG. 11A is a perspective view of a kit within the vasculature of apatient, wherein the kit includes a laser catheter radially disposedwithin a sheath and over a guidewire, according to one embodiment of thepresent disclosure, wherein the kit and guidewire are located proximallyof a vascular occlusion;

FIG. 11B is a perspective view of a kit within the vasculature of apatient, wherein the kit includes a laser catheter radially disposedwithin a sheath and over a guidewire, according to one embodiment of thepresent disclosure, wherein the kit is located proximally of a vascularocclusion, and the guidewire has penetrated the vascular occlusion;

FIG. 11C is a perspective view of a kit within the vasculature of apatient, wherein the kit includes a laser catheter radially disposedwithin a sheath and over a guidewire, according to one embodiment of thepresent disclosure, wherein the sheath is located proximally of avascular occlusion, and the laser catheter and guidewire have penetratedthe vascular occlusion;

FIG. 11D is a perspective view of a kit within the vasculature of apatient, wherein the kit includes a laser catheter radially disposedwithin a sheath and over a guidewire, according to one embodiment of thepresent disclosure, wherein the kit and guidewire have penetrated thevascular occlusion;

FIG. 12 is a representative flow diagram of a method of treating asubject using a laser catheter and sheath, according to one embodimentof the present disclosure;

FIG. 13 is an elevation view of a kit that includes a laser catheterradially disposed within a sheath and over a guidewire, according to oneembodiment of the present disclosure;

FIG. 14A is an elevation view of a kit that includes a laser catheterradially disposed within a handle and a sheath and over a guidewire,according to one embodiment of the present disclosure;

FIG. 14B is a detail elevation view of the laser catheter and the handleof FIG. 14A at a proximal end of the handle;

FIG. 15A is a perspective view of the handle of FIG. 14A, whereinseveral external components are partially transparent to illustrateinternal components, and a shaft of the handle is shown in a proximalposition;

FIG. 15B is another perspective view of the handle of FIG. 14A, whereinseveral external components are partially transparent to illustrateinternal components, and the shaft is shown in the proximal position;

FIG. 15C is an elevation view of the handle of FIG. 14A, wherein severalexternal components are partially transparent to illustrate internalcomponents, and the shaft is shown in the proximal position;

FIG. 15D is an elevation view of the handle of FIG. 14A, wherein severalexternal components are partially transparent to illustrate internalcomponents, and the shaft is shown in an intermediate position;

FIG. 15E is an elevation view of the handle of FIG. 14A, wherein severalexternal components are partially transparent to illustrate internalcomponents, and the shaft is shown in a distal position;

FIG. 15F is a cross-sectional view of the handle of FIG. 14A, whereinthe shaft is shown in the proximal position;

FIG. 15G is a cross-sectional view of the handle of FIG. 14A, whereinthe shaft is shown in an intermediate position;

FIG. 15H is an exploded view of the handle of FIG. 14A;

FIG. 15I is a detail exploded view of the handle of FIG. 14A;

FIG. 15J is another detail exploded view of the handle of FIG. 14A;

FIG. 16A is a perspective view of a frame of the handle of FIG. 14A;

FIG. 16B is an elevation cross-sectional view of the frame along line16B-16B of FIG. 16A;

FIG. 16C is a perspective cross-sectional view of the frame along line16B-16B of FIG. 16A;

FIG. 16D is an elevation cross-sectional view of the frame along line16D-16D of FIG. 16A;

FIG. 16E is a perspective cross-sectional view of the frame along line16D-16D of FIG. 16A;

FIG. 16F is an elevation cross-sectional view of the frame along line16F-16F of FIG. 16A;

FIG. 16G is a perspective cross-sectional view of the frame along line16F-16F of FIG. 16A; and

FIG. 17 is an elevation cross-sectional view of the shaft of the handleof FIG. 14A.

FIG. 18 is a perspective view of an outer sheath comprising aattenuating member, according to one embodiment of the presentdisclosure;

FIG. 18A is a side elevation view of an attenuating member comprising aplurality of square-shaped openings, according to one embodiment of thepresent disclosure;

FIG. 18B is a side elevation view of an attenuating member comprising aplurality of diamond-shaped openings, according to one embodiment of thepresent disclosure;

FIG. 18C is a side elevation view of an attenuating member comprising aplurality of openings formed by a helical structure wound in aparticular direction, according to one embodiment of the presentdisclosure;

FIG. 18D is a side elevation view of an attenuating member comprising aplurality of openings formed by a helical structure wound in aparticular direction, according to one embodiment of the presentdisclosure;

FIG. 18E is a side elevation view of an attenuating member comprising aplurality of openings formed by a helical wound ribbons, according toone embodiment of the present disclosure;

FIG. 18F is a side elevation view of an attenuating member comprising aplurality of hexagon-shaped openings, according to one embodiment of thepresent disclosure; and

FIG. 19 is a representative flow diagram of a method of treating asubject using a laser catheter and sheath, according to one embodimentof the present disclosure.

FIG. 20 is a representative cross-sectional view of the distal end of acatheter, according to one embodiment of the present disclosure.

FIG. 20′ is a representative cross-sectional view of the distal end ofthe catheter illustrated in FIG. 20, according to an alternateembodiment of the present disclosure.

FIG. 20″ is a representative cross-sectional view of the distal end ofthe catheter illustrated in FIG. 20, according to another alternateembodiment of the present disclosure.

FIG. 20′″ is a representative cross-sectional view of the distal end ofthe catheter illustrated in FIG. 20, according to yet another alternateembodiment of the present disclosure.

FIG. 21 is a representative side view of a catheter system including alaser catheter and a sheath having a sealable valve, according to anembodiment of the present disclosure.

FIG. 22 is an enlarged representative perspective view of the sealablevalve of the catheter system depicted in FIG. 21.

FIG. 22A is an enlarged representative cross-sectional side view of thesealable valve of the catheter system depicted in FIG. 21 in an unsealedconfiguration with respect to a guidewire.

FIG. 22B is an enlarged representative cross-sectional side view of thesealable valve of the catheter system depicted in FIG. 21 in a sealedconfiguration with respect to a guidewire.

FIG. 23 is a representative side view of a catheter system including alaser catheter, a sheath having a sealable valve, and a light absorbingmaterial support structure, according to an embodiment of the presentdisclosure.

FIG. 24 is a cross-sectional view of a distal portion of a cathetersystem including a light absorbing material support structure, accordingto one embodiment of the present disclosure.

FIG. 25 is a cross-sectional view of an arterial wall taken along adirection perpendicular to the longitudinal axis of the arterial wall.

FIG. 25A is reduced version of the cross-sectional view of the arterialwall in FIG. 25.

FIG. 26A is a longitudinal-sectional view of a healthy arterial walltaken along a direction parallel to the longitudinal axis of thearterial wall.

FIG. 26B is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterialwall, wherein the arterial wall includes fat and/or lipids.

FIG. 26C is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterialwall, wherein the arterial wall includes plaque and calcium in theintima.

FIG. 26D is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterialwall, wherein the arterial wall includes calcified plaque and lipids inthe intima.

FIG. 26E is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterialwall, wherein the arterial wall has ruptured.

FIG. 26F is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterialwall, wherein the artery includes an occlusion.

FIG. 26G is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallwith a laser catheter removing the occlusion depicted in FIG. 21F.

FIG. 26H is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallwith a sheath and laser catheter located adjacent the remaining portionof the vascular occlusion depicted in FIG. 26G, wherein the end of thelaser catheter, particularly its emitter(s) is disposed distally of themost distal end of the sheath.

FIG. 26H′ is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallwith a sheath and laser catheter located adjacent the remaining portionof the vascular occlusion depicted in FIG. 26G, wherein the end of thelaser catheter, particularly its emitter(s), is disposed within andproximally of the most distal end of the sheath.

FIG. 26I is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallafter utilizing a sheath and laser catheter illustrated in FIG. 26H andor FIG. 26H′.

FIGS. 27A and 27B are a method of removing restriction vascularocclusion and treating the remainder of the vascular occlusion withinthe intima with a sheath and laser catheter.

FIG. 28A is a longitudinal-sectional view of a healthy arterial walltaken along a direction parallel to the longitudinal axis of thearterial wall similar to the arterial wall depicted in FIG. 26A.

FIG. 28B is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallwith calcification of the media portion of the blood vessel.

FIG. 28C is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallwith a sheath and laser catheter located adjacent the portion of thearterial wall that includes the calcified media portion of the bloodvessel.

FIG. 28D is a longitudinal-sectional view of an arterial wall takenalong a direction parallel to the longitudinal axis of the arterial wallthat includes disrupted calcified media after being treated with asheath and laser catheter;

FIG. 29 is a method of using a sheath and laser catheter to treat thecalcified media portion of the blood vessel.

FIG. 30 is a kit that includes a laser catheter assembly and an outersheath assembly.

FIG. 30A is an enlarged view of the distal portions of the lasercatheter assembly and an outer sheath assembly within line 30A-30A ofFIG. 30, wherein the laser catheter assembly extends beyond the distalend of the outer sheath assembly, and wherein a portion of the outersheath assembly is illustrated in a translucent material for purposes ofclarifying the figure.

FIG. 30B is an enlarged longitudinal sectional view of the distalportions of the laser catheter assembly and outer sheath assemblydepicted in FIG. 30A taken along line B-B, wherein the laser catheterassembly is disposed within the outer sheath assembly and extends beyondthe distal end of the outer sheath assembly.

FIG. 30B′ is an enlarged longitudinal sectional view of the distalportions of the laser catheter assembly and outer sheath assemblydepicted in FIG. 30A, wherein the laser catheter assembly is disposedwithin the outer sheath and the distal end of the laser catheterassembly is proximal of the distal end of the outer sheath assembly.

FIG. 31 is the outer sheath assembly depicted in FIG. 30.

FIG. 31A is an enlarged view of the distal portion of the outer sheathassembly within line 31A-31A of FIG. 31, wherein a portion of the outersheath assembly is illustrated in a translucent material for purposes ofclarifying the figure.

FIG. 31B is an enlarged longitudinal sectional view of the distalportion of the outer sheath assembly depicted in FIG. 31A taken alongline B-B.

FIG. 31C is an enlarged longitudinal sectional view of the distalportion of the outer sheath assembly within line 31C-31C of FIG. 31B.

FIG. 31C′ is an alternative embodiment of an enlarged longitudinalsectional view of the distal portion of the outer sheath assemblydepicted in FIG. 31B.

FIG. 32 is the laser catheter assembly depicted in FIG. 30.

FIG. 32A is an enlarged view of a distal portion of the laser catheterassembly within line 32A-32A of FIG. 32.

FIG. 33 is a flow chart illustrating the steps of a method of using akit that includes a laser catheter assembly and an outer sheathassembly.

FIG. 34A is an enlarged view of a distal portion of another kit thatincludes a laser catheter assembly and an alternative embodiment of theouter sheath assembly, wherein the laser catheter assembly is disposedwithin the outer sheath assembly and proximal of the distal end of theouter sheath assembly.

FIG. 34B is an enlarged view of a distal portion of the kit in FIG. 34A,wherein the laser catheter assembly is disposed within the outer sheathand extends beyond the distal end of the outer sheath assembly.

FIG. 35 is an enlarged view of a distal portion of another kit thatincludes a laser catheter assembly and an alternative embodiment of theouter sheath assembly, wherein the laser catheter assembly is disposedwithin the outer sheath and proximal of the distal end of the outersheath assembly.

FIG. 36A is an enlarged view of a distal portion of another kit thatincludes a laser catheter assembly and an alternative embodiment of theouter sheath assembly, wherein the laser catheter assembly is disposedwithin the outer sheath assembly and proximal of the distal end of theouter sheath assembly.

FIG. 36B is an enlarged view of a distal portion of the kit in FIG. 36A,wherein the laser catheter assembly is disposed within the outer sheathassembly in a position further distally than that in FIG. 36A butproximal of the distal end of the outer sheath assembly.

FIG. 37A is an enlarged view of a distal portion of another kit thatincludes a laser catheter assembly and an alternative embodiment of theouter sheath assembly, wherein the laser catheter assembly is disposedwithin the outer sheath and proximal of the distal end of the outersheath assembly.

FIG. 37B is an enlarged view of a distal portion of the kit in FIG. 37A,wherein the laser catheter assembly is disposed within the outer sheathassembly and extends beyond the distal end of the outer sheath assembly.

FIG. 38 is an enlarged view of a flat wire disposed within one or moreembodiments of the outer sheath assembly.

FIG. 39 is an outer sheath for a kit that also includes a laser catheterassembly.

FIG. 39A is an enlarged longitudinal sectional view of a distal portionof the outer sheath along line 39A-39A of FIG. 39.

FIG. 40 is an enlarged partially exploded view illustrating variouslayers of the outer sheath of FIG. 39.

FIG. 41 is an elevation view of a laser catheter system or a kit thatincludes a laser catheter radially disposed within a handle and asheath, according to one embodiment of the present disclosure.

FIG. 42 is a schematic illustration of a treatment mode selection systemof the laser catheter system of FIG. 41.

FIG. 43 is an elevation view of a laser catheter system or a kit in afirst configuration, the system including a laser catheter radiallydisposed within a handle and a sheath, according to one embodiment ofthe present disclosure.

FIG. 44 is a perspective view of the laser catheter system of FIG. 43 inthe first configuration.

FIG. 45 is an elevation view of the laser catheter system of FIG. 43 ina second configuration.

FIG. 46 is a perspective view of the laser catheter system of FIG. 43 inthe second configuration.

DETAILED DESCRIPTION

The present disclosure relates generally to the use of medical devicesfor the treatment of vascular conditions. In particular, the presentdisclosure provides materials and methods for using laser-inducedpressure waves to disrupt vascular blockages and to deliver therapeuticagents to the blockage area.

Referring to FIG. 1, there is depicted an exemplary ablation system 100of the present disclosure. Ablation system 100 includes a laserapparatus 130 coupled to a laser controller 175. Controller 175 includesone or more computing devices programmed to control laser 130.Controller 175 may be internal or external to laser apparatus 130, suchas a laser generator. Laser apparatus 130 may include an excimer laseror another suitable laser. In some embodiments, laser 130 produces lightin the ultraviolet frequency range. In one embodiment, laser 130produces optical energy in pulses.

Laser 130 is connected with the proximal end of a laser energy deliverysystem 120, illustratively a laser catheter 170 via coupler 140. Lasercatheter 170 includes one or more optical energy transport devices whichreceive laser energy from laser 130 and transports the received laserenergy from a first, proximal end 124 of laser energy catheter 170towards a second, distal end 126 of laser catheter 170. The distal endof catheter 170 may be inserted into a vessel or tissue of a human body110. In some embodiments, system 100 employs a plurality of light guidesas the optical energy transport devices, such as optical fibers, thatguide laser light from laser 130 through catheter 170 toward a targetarea in human body 110.

Exemplary laser catheter devices or assemblies may include lasercatheters and/or laser sheaths. Examples of laser catheters or lasersheath are sold by The Spectranetics Corporation under the tradenamesELCA™ and Turbo Elite™ (each of which is used for coronary interventionor peripheral intervention, respectively, such as recanalizing occludedarteries, changing lesion morphology, and facilitating stent placement)and SLSII™ and GlideLight™ (which is used for surgically implanted leadremoval). The working (distal) end of a laser catheter typically has aplurality of laser emitters that emit energy and ablate the targetedtissue. The opposite (proximal) end of a laser catheter typically has afiber optic coupler 140 and an optional strain-relief member 124. Thefiber optic coupler 140 connects to a laser system or generator 130. Onesuch example of a laser system is the CVX-300 Excimer Laser System,which is also sold by the Spectranetics Corporation.

The laser controller 175 of FIG. 1 includes a non-transitorycomputer-readable medium (for example, memory 204) that includesinstructions that, when executed, cause one or more processors 200 tocontrol laser 130 and/or other components of ablation system 100.Controller 175 includes one or more input devices 206 to receive inputfrom an operator. Exemplary input devices include keys, buttons, touchscreens, dials, switches, mouse, and trackballs which providing usercontrol of laser 130. Controller 175 further includes one or more outputdevices to provide feedback or information to an operator. Exemplaryoutput devices include a display, lights, audio devices which provideuser feedback or information.

A laser source of laser 130 is operatively coupled to laser controller175. Laser source is operative to generate a laser signal or beam andprovide the laser signal through a fiber optic bundle of catheter 170 tothe human. Fiber optic bundle serves as delivery devices for deliveringthe laser signal to the target area of the human body 110.

FIG. 1 depicts the catheter 170 entering the leg, preferably through thefemoral artery, of the human body. As discussed above, it may bedesirable to treat either CAD or PAD. After entering the femoral artery,it the catheter 170 is intended to treat CAD, the catheter 170 will bedirected through the patient's vasculature system and to the coronaryarteries. Alternatively, if the catheter 170 is intended to treat PAD,the catheter 170 will be directed through the patient's vasculaturesystem and to the peripheral arteries, such as the vasculature below theknee, particularly the vasculature in the patient's legs and/or feet.Unlike balloon catheters, the catheter 170 of the present disclosure isable to more easily navigate and enter smaller sized vasculature becausethe overall diameter of the sheath is smaller in comparison to ballooncatheters, thereby allowing the catheter 170 of the present disclosuremore easily treat PAD. That is, the increased size of a balloon of anelectrically-induced shockwave balloon catheter and/or a typicaldilation balloon catheter (in comparison to the catheter 170 of thepresent disclosure) may prevent or increase the difficulty of theballoon-type catheter from entering, penetrating and/or treating theperipheral vasculature, such the vasculature below the knee in the legsand/or feet.

Referring to FIGS. 2A, 2B, 2C and 2D, there is depicted an embodiment ofthe catheter 170 of the present disclosure. The catheter 170 of thepresent disclosure may include an outer sheath 182, an inner sheath 184,one or more optical fibers 186, and a tip 180. The outer sheath 182,inner sheath 184, and one or more optical fibers 186 generally span thelength of the catheter 170, and each have a proximal end and a distalend. The inner sheath 184 is disposed concentrically and/or radiallywithin the outer sheath 182, and the one or more optical fibers 186 aredisposed concentrically and/or radially within the inner sheath 184.

As depicted in FIG. 2C, at the distal end 126 of the catheter 170, thedistal end of the outer sheath 182 is directly coupled to the tip 180.The inner sheath 184 and the one or more optical fibers 186 are notdirectly coupled to the tip 180. Rather, the inner sheath 184 and theone or more optical fibers 186 are disposed proximate the tip 180,thereby forming a cavity among the outer sheath 182, the inner sheath184, one or more optical fibers 186, and the tip 180.

The inner sheath 184, which is constructed of a biocompatible polymerhas one or more lumens 190, which are used to deliver a liquid medium tothe cavity, thereby partially or completely filling the cavity with theliquid medium. The liquid medium is introduced to the catheter 170through one or more liquid medium ports (not shown) in fluidcommunication with the one or more lumens 190 within the inner sheath184 and disposed about the outer sheath 182. The liquid medium ports mayalso serve as a means for removing the liquid medium from the catheter170.

The liquid medium is configured to absorb light energy and therebyproduce laser-induced pressure waves in the liquid medium. Thelaser-induced pressure wave compresses the fluid surrounding its origin,thereby generating a vapor bubble. As the laser-induced pressure wavepropagates away from its origin, the fluid surrounding the vapor bubbledisplaces inwardly, collapsing the vapor bubble and creating acavitation event. The vapor bubble and subsequent cavitation event(s)are byproducts of the laser-induced pressure wave. And the subsequentcavitation event(s) produce additional resultant pressure waves that aretransmitted to the tip 180 and/or the outer sheath 182 to disrupt avascular occlusion.

Liquid medium can include contrast medium, including for example,iodine-containing contrast medium or gadolinium contrast medium, as wellas contrast solutions comprising dye(s) and/or particle(s).Additionally, any liquid medium can be used, as long as the liquidmedium is coupled with a light source, such as emitters coupled to theone or more optical fibers, which emits light at a suitable wavelengthsuch that the liquid absorbs the light, produces laser-induced pressurewaves, vapor bubbles, and cavitation events that produce additionalresultant pressure waves. In some cases, the liquid medium can becontrast medium (for example, iodine-containing contrast medium orgadolinium contrast medium) and/or the liquid medium can be a contrastsolution comprising a biocompatible fluid (for example, saline) in whicha contrast dye(s) or particle(s) have been mixed at variousconcentrations.

As mentioned above, one or more optical fibers 186 are disposed withinthe inner sheath 184 extending from a proximal portion of the innersheath 184 to the distal end of the inner sheath 184 and into thecavity. The proximal end of the one or more optical fibers is coupled tothe laser generator 130. The distal end(s) of the one or more opticalfibers 186 are proximate, at, or distal the distal end of the innersheath 184. Again, one or more emitters are disposed at the distal endof the one or more optical fibers 186. The emitter(s) are in directcontact with the liquid medium, such that when laser light energy isemitted from the emitter(s), the liquid medium absorbs the emittedlight, which in turn produces laser-induced pressure waves and generatesvapor bubbles and cavitation events that produce additional pressurewaves.

To treat a subject having a vascular occlusion, the tip 180 of thecatheter 170 is positioned adjacent to the vascular occlusion. When thelaser system 130 is activated, light energy travels through one or moreoptical fibers until the light energy is released from the emitter. Asthe liquid medium absorbs the light energy, laser-induced pressure wavesare produced. Additionally, the liquid medium rapidly displaces outwardsand inwards, creating vapor bubbles. The energy produced by thelaser-induced pressure waves is captured within the cavity and convertedto mechanical energy via moving the tip 180 and/or transferred to thevascular occlusion through the tip 180. The transfer of the energyproduced by the laser-induced pressure waves to the vascular occlusionis sufficient to disrupt vascular occlusion, particularly the calcifiedand/or fibrous (for example, calcium deposits) portions of a totalocclusion. It is desirable for the mechanical energy created at the tip180 by the laser-induced pressure waves and resulting fluid displacementto be transferred to the occlusion. Accordingly, when the energyproduced by the laser-induced pressure waves is captured within thecavity, it is desirable for the forces generated by the laser-inducedpressure waves to propagate longitudinally, including in a forward (thatis, parallel with the vessel) direction, thereby increasing the tip'sability to disrupt, destroy and/or penetrate the vascular occlusion.That is, as the laser-induced pressure waves are produced, the tip 180of the catheter rapidly moves (translates) forwards and backwardstowards and away from, respectively, the occlusion. Pressure wavesproduced in this manner can also be used to increase vessel complianceprior to performing another procedure, such as a traditional balloonangioplasty or drug eluting balloon treatment.

In order to facilitate the direction in which the forces that areproduced by the laser-induced pressure waves translate into the movementof the tip 180 in a forward/backward longitudinal direction, the outersheath 182 is not only flexible, but the outer sheath 182 also has theability to expand and contract in a longitudinal direction. One exampleof such an outer sheath 182 includes a slotted or laser-cut hypotubeconstructed of a biocompatible material, such as stainless steel, or abiocompatible polymer. The hypotube has spring-like characteristics,which allow it to expand and contract in a longitudinal direction.Specifically, the slotted or laser cut pattern in the hypotube allows itto expand and contract. Another example of the outer sheath 182 mayinclude of one or more spirally wound wires, thereby creating a coiledsheath, which also has the ability to expand and contract in alongitudinal direction.

In order to further facilitate the movement of the tip 180 in alongitudinal direction, it may be desirable to include a shield 188disposed axially between the distal end of the inner sheath 184 and theproximal end of the tip 180, and disposed radially between the one ormore optical fibers 186 and the outer sheath 182. As illustrated in FIG.2C, the shield 188, which is depicted as a generally cylindrical tube,may increase the laser-induced pressure waves' resistance in the radialdirection, thereby reducing the ability of the laser-induced pressurewaves to travel radially towards the outer sheath 182 and mayconcentrate the energy produced by the laser-induced pressure waves inthe longitudinal direction. The configuration of thecylindrically-shaped shield 188 may allow for a reduced resistance inthe longitudinal direction, in comparison to the radial direction,thereby potentially increasing the energy produced by the laser-inducedpressure waves in the longitudinal direction and increasing the tip'sability to translate in a forward/backward direction. Thecylindrically-shaped shield 188 may also be configured such that itsdiameter is greater at its proximal end in comparison to its distal end,thereby potentially concentrating the laser-induced pressure wavestowards the center of the tip 180. Or the cylindrically-shaped shield188 may be configured such that its diameter is less its proximal end incomparison to its distal end, thereby potentially concentrating thelaser-induced pressure waves towards the center of the tip 180.

The tip 180 illustrated in FIGS. 2B & 2C has a closed configuration.However, the present disclosure contemplates that the tip can also havean open configuration. Additionally, the tip 180 illustrated in FIGS. 2B& 2C is a separate component from the distal end 126 of laser catheter170 and is coupled to the distal end 126. However, the presentdisclosure contemplates that the tip can also be integral with thedistal end 126 of the laser catheter 170. The tip 180 illustrated inFIGS. 2B & 2C is generally tapered from a larger diameter to a smallerdiameter as the tip progresses distally. Additionally, the shape of thetip 180 shown in FIGS. 2B & 2C is generally conical. Furthermore, thetip 180 has a completely solid configuration, but it may be also bepartially solid. It is desirable for the tip to be constructed of abiocompatible material, such as stainless steel or a biopolymer.

Similar to the tip 180 illustrated in FIGS. 2B & 2C, the tip 180′ inFIGS. 2B′ & 2C′ has a completely solid configuration, but the tip 180′in FIGS. 2B′ & 2C′ may alternatively have a partially solidconfiguration. Unlike the tip 180 illustrated in FIGS. 2B & 2C, the tip180′ in FIGS. 2B′ & 2C′ may have a generally convex, spherical shape.Although the present disclosure only depicts a generallyconically-shaped tip 180 in FIGS. 2B & 2C and a generallyspherically-shaped tip 180′ in FIGS. 2B′ & 2C′, the tip may havealternative shapes, such as a flat shape, concave shape, triangularshape, a pyramid shape, chisel, etc.

Referring to FIG. 3, there is depicted an alternative embodiment of thecatheter of the present disclosure. Similar to the tip 180′ in FIGS. 2B′& 2C′, the tip 380 in FIG. 3 has a generally spherical shaped. However,unlike the tip 180′ in FIGS. 2B′ & 2C′, which has a solid configuration,the tip 380 in FIG. 3 has a hollow or shell-type configuration. Also,the tip 280 in this embodiment, as well as the other embodiments, may bepress fit and/or welded to the outer sheath 182″.

The embodiments of the catheter depicted in FIGS. 2B & 2C and FIGS. 2B′& 2C′ and FIG. 3 include a shield 188. However, it may not be necessaryto include a shield within the catheter. For example, FIG. 4 illustratesan embodiment of the catheter 170 in which the shield is omitted fromthe distal tip of the catheter. As depicted in this figure, in the eventthat a shield is omitted, it may be desirable for the outer sheath 182′″to include a solid portion between the distal end of the inner sheath184′″ and the proximal end of the tip 480 in order to create anon-porous cavity.

Referring to FIGS. 5, 5A and 5A′, the distal end 526 of the catheter mayinclude a tip 580 that comprises a non-metallic component in lieu of ametallic (for example, stainless steel) solid or hollow construction.Referring to FIG. 5A, the catheter includes an outer sheath 582, aninner sheath 584 disposed concentrically and/or radially within theouter sheath 582, and one or more optical fibers 586 disposedconcentrically and/or radially within the inner sheath 584. The distalend of the outer sheath 582 is directly coupled (via a press fit and/ora weld) to the tip 580. The inner sheath 584 and the one or more opticalfibers 586 are not directly coupled to the tip 580. Rather, the innersheath 584 and the one or more optical fibers 586 are disposed proximatethe tip 580, thereby forming a cavity among the outer sheath 582, theinner sheath 584, one or more optical fibers 586, and the tip 580.

Continuing to refer to FIG. 5A, the catheter may include a shield 588disposed axially between the distal end of the inner sheath 584 and theproximal end of the tip 580, and disposed radially between the one ormore optical fibers 586 and the outer sheath 582. As illustrated in FIG.5A, the shield 588, which is depicted as a generally cylindrical tube,increases the laser-induced pressure waves' resistance in the radialdirection, thereby reducing the ability of the laser-induced pressurewaves to travel radially towards the outer sheath 582. The configurationof the cylindrically-shaped shield 588 allows for a reduced resistancein the longitudinal direction, in comparison to the radial direction,thereby increasing the tip's ability to translate in a forward/backwarddirection. The cylindrically-shaped shield 588 may also be configuredsuch that its diameter is greater (or less) at its proximal end incomparison to its distal end, thereby potentially tapering in either theproximal or distal direction and concentrating the laser-inducedpressure waves towards the center of the tip 580. The shield 588 mayalso serve to create a sealed cavity at the distal end of the catheter,thereby preventing the leakage of the liquid medium through the outersheath 582 because a portion of the shield overlaps with a portion ofthe outer sheath 582 that may be porous. Referring to FIG. 5A′, if theshield is omitted, it may be desirable for the outer sheath 582 toinclude a solid or non-porous sheath portion between the distal end ofthe inner sheath 584 and the proximal end of the tip 580 in order tocreate a non-porous cavity.

The inner sheath also includes one or more lumens for passage of liquidmedium into the cavity. The distal end(s) of the one or more opticalfibers 586 are proximate, at, or distal the distal end of the innersheath 584. Again, one or more emitters are disposed at the distal endof the one or more optical fibers 586. The emitter(s) are in directcontact with the liquid medium, such that when laser light energy isemitted from the emitter(s), the liquid medium absorbs the emittedlight, which in turn produces laser-induced pressure waves and generatespressure waves and/or vapor bubbles that produce additional pressurewaves and/or one or more cavitation events.

As depicted in FIGS. 5A and 5A′, the tip 580 has a circularconstruction, thereby creating a collar for the distal end of the outersheath 582. The tip 580 also includes a flexible membrane 585 at itsdistal end. For example, the membrane 585 may be constructed of Mylarand be adhesively bonded to the distal end of the tip 580 in anorientation perpendicular to the longitudinal axis. In addition themembrane may be compliant in order to form against and engage the shapeof the calcified cap, total occlusion or lesion.

To treat a subject having a vascular occlusion, the distal end of thecatheter, particularly the tip 580 is positioned adjacent to thevascular occlusion with the membrane adjacent the vascular occlusion.The liquid medium is delivered to the cavity from the one more lumenswithin the inner sheath 584 through one or more liquid medium ports orbetween the outer sheath and the inner sheath or laser catheter. Whenthe laser system 130 is activated, light energy travels through one ormore optical fibers until the light energy is released from theemitter(s) at the end of the one or more optical fibers. As the liquidmedium absorbs the light energy, a lase-induced pressure wave forms, theliquid medium rapidly displaces outward and then inwardly, therebycreating a vapor bubble. The energy produced by the laser-inducedpressure wave and vapor bubble is captured within the closed systemprovided by the cavity and transferred to the vascular occlusion throughthe flexible membrane 585 of the tip 580. The transfer of the energyproduced by the laser-induced pressure waves to the vascular occlusionis sufficient to disrupt calcium deposits and/or fibrous tissue withinthe vascular occlusion. The forces generated by the laser-inducedpressure waves can propagate longitudinally forward (that is, parallelto the vessel). Laser-induced pressure waves produced in this manner canalso be used to increase vessel compliance prior to performing anotherprocedure, such as a traditional balloon angioplasty.

The embodiments of the catheters discussed hereinabove with respect toFIGS. 1-5 are integral catheters, such that the optical fiber(s) areintegrated within the design of a single catheter. The presentdisclosure, however, also encompasses a two-piece catheter system orkit. Referring to FIGS. 6 and 6A, the catheter system may include alaser catheter 650 and a tubular sheath 682 having a lumen thereinand/or therethrough and configured to surround the laser catheter 650.Depending upon whether the tubular sheath 682 has an open or closeddistal end, the tubular sheath 682 may be coupled to a tip 680. Atraditional laser catheter 650, including one or more optical fibers686, can be inserted within the lumen, thereby allowing a clinician totranslate the laser catheter 650 within sheath 682 along thelongitudinal axis of the sheath in a forward (distal) and backwards(proximal) direction. For the purposes of this disclosure, the lasercatheter 650 may include one or more one more lumens 690 to deliver theliquid medium from the one or more liquid medium ports. When the lasersystem 130 is activated, light energy travels through one or moreoptical fibers until the light energy is released from the emitter(s) atthe end of the one or more optical fibers. As the liquid medium absorbsthe light energy, a laser-induced pressure wave forms, the liquid mediumrapidly displaces outward then inward, thereby creating a vapor bubble.The energy produced by the laser-induced pressure wave and vapor bubbleis captured within the closed system provided by the cavity andtransferred to the vascular occlusion through the walls of the sheath682 and/or the tip 680. The transfer of the energy produced by thelaser-induced pressure waves to the vascular occlusion is sufficient todisrupt calcium deposits and/or fibrous tissue within the vascularocclusion. Depending upon the location of the emitter(s) within lumen ofthe sheath 682, a smaller or larger cavity is created among the distalend of the laser catheter 650, the tip 680, and the sheath 682. It maydesirable for the distal end of the laser catheter 650 to be disposedproximal of the tip 680 or translated inside of the outer sheath tocreate a cavity with which the forces generated by the laser inducedpressure wave can propagate radially from multiple axial positions alongthe longitudinal axis of the outer sheath.

Depending upon the location of the emitter(s) within lumen of the sheath682, the forces generated by the laser-induced pressure waves maypropagate radially, including in forward (that is, parallel to thevessel), upward (that is, perpendicular to the vessel), and backward(that is, proximally) directions. As depicted in FIG. 6, when the lasercatheter 650 is disposed proximate the tip 680, the laser-inducedpressure waves may propagate radially from the sheath 650 and forward(that is, parallel to the vessel) from the tip. As depicted in FIG. 6A,upon the laser catheter 650 translating proximally along thelongitudinal axis of the lumen within the sheath 682 in comparison tothe position of the laser catheter 650 in FIG. 6, the laser-inducedpressure waves may propagate in a direction radially from the sheath650, forward (that is, parallel to the vessel), upward (that is,perpendicular to the vessel), and/or backward (that is, proximally).Accordingly, after the tip 680 of the sheath 682 destroys the calcifiedand/or fibrous tissue within the vascular occlusion, the sheath 682 maypenetrate and cross the occlusion, and the laser catheter 650 can slidein proximal and/or distal direction to destroy additional portions ofthe occlusion.

Referring to FIG. 6B, the laser catheter 650′ may also include adeflector 692 attached to its distal end via at least one, and possiblya plurality of, support member(s) 696, 698. The purpose of the deflectoris to direct the laser-induced pressure wave generated by theinteraction between the liquid medium and the emitters from one or moreoptical fibers 686′ within the liquid medium in a particular direction.In this figure, the deflector 692 is positioned along the longitudinalaxis of the laser catheter 650′, but the shape of the deflector 692 isoriented in a radial direction that is perpendicular to longitudinalaxis of the laser catheter 650′. Accordingly, as the laser-inducedpressure waves are produced from the interaction between the liquidmedium and the laser light energy emitted from the emitters, thedeflector 692 may direct the laser-induced pressure waves in a radialdirection, such as 360 degrees about the circumference of the lasercatheter 650′ and/or sheath 682. The deflector 692 may be constructed ofa non-metallic material or a metallic material, such as stainless steel.The deflector 692 may also have a solid or porous construction.Regardless of the construction of the deflector 692, the deflector 692shall direct the laser-induced pressure waves in a particular directionthat is in an advantageous direction, such as toward the vascularocclusion, which may be on the side of the sheath 682.

Various shapes and configurations of deflectors are envisioned. Forexample, referring to FIG. 7, the laser catheter 750 may include adeflector 792 disposed distally from the one or more optical fibers 786of the laser catheter 750, may be configured to direct the laser-inducedpressure waves in a radial direction less than 360 degrees (for example,5 degrees, 10 degrees, 15 degrees, . . . , 30 degrees, . . . , 45degrees, . . . , 60 degrees, . . . , 75 degrees, . . . , 90 degrees, . .. , 105 degrees, . . . , 120 degrees, . . . , 135 degrees, . . . , 150degrees, . . . , 165 degrees, . . . , 180 degrees, etc.) about thecircumference of the laser catheter 750 and/or sheath 782. For example,the deflector 792 may have a solid construction with an opening facing aparticular direction. And the shape and size of the opening within thedeflector may dictate the direction that the laser-induced pressurewaves may travel. As depicted in FIG. 7, the laser catheter 750 maytranslate axially within the sheath 782 along the longitudinal axis ofthe laser catheter 750 and/or sheath 782. The present disclosure alsocontemplates that the laser catheter 750 may rotate within the sheath782 about the longitudinal axis of the laser catheter 750 and/or sheath782, thereby directing not only directing the laser-induced pressurewaves along a longitudinal direction but also about a radial direction.

The transfer of the energy produced by the creating a laser-inducedpressure wave to the vascular occlusion and/or to the walls of thevessel is sufficient to disrupt intraluminal calcium as well as calciumwithin the tissue of the blood vessel, vascular occlusion (for example,calcium deposits). The forces generated by the laser-induced pressurewave can propagate radially, including in forward (that is, parallel tothe vessel), upward (that is, perpendicular to the vessel), and backward(that is, proximally) directions. Laser-induced pressure waves producedin this manner can also be used to increase vessel compliance prior toperforming another procedure, such as a traditional balloon angioplasty,drug-eluting balloon angioplasty and/or stent placement. That is, thelaser-induced pressure wave disruption of the intraluminal calciumand/or calcium within the tissue of the blood vessel and the vascularocclusion, can improve the vasculature's ability to absorb drugs,particularly when such drugs are applied with a drug eluting balloon.

Referring again to FIGS. 6 and 6A, the catheter system includes thelaser catheter 650 disposed within the sheath 682 and proximate the tip680, thereby allowing the laser-induced pressure waves to propagateradially from the sheath 650 and forward (that is, parallel to thevessel) from the tip. In order to ensure that the laser catheter 650 isproximate the tip 680 to create a cavity between the distal end of thelaser catheter 650, the sheath 682 and the tip 680, the laser catheter650 and/or the sheath 682 may include stops and/or matingly engageablesprings and/or recesses to maintain the laser catheter 650 at thedesirable distance proximate the tip 680. The stops and/or matinglyengageable springs and/or recesses shall also be configured to allow theclinician to easily disengage the laser catheter 650 from the sheath 682so the laser catheter 650 may translate within the sheath 682.

Referring to FIGS. 8 and 8A, if it is not desirable to slide the lasercatheter within the sheath, then the laser system may include lasercatheter 850 that is engageable with and removable from a cap 870. Thecap 870 may include a relatively short sheath attached to a tip 880 andan optional shield 888. Similar to the embodiment in FIGS. 6 and 6A, theembodiment in FIGS. 8 and 8A may include matingly engageable springsand/or recesses that are configured to allow the clinician to easilyengage and disengage the laser catheter 850 from the cap 870.

The laser catheter 850 may include one or more layers of optical fibers854 arranged circumferentially around or adjacent to an optional innerlumen, which may be used to insert a guidewire and/or the liquid medium.Or the laser catheter 850 may include one or more additional lumens toserve independent purposes. Again, the proximal end of the lasercatheter is coupled to a laser generator. The one or more layers ofoptical fibers 854 are housed in a flexible tubular catheter andterminate at the distal emitter at the distal tip 856 of the lasercatheter 850. The liquid medium travels through the lumen 852 untilbeing introduced from one or more liquid medium ports (not shown) intothe cavity. The emitter is in direct contact with the liquid medium suchthat when laser light energy is emitted from the proximal emitter, theliquid medium absorbs the emitted light, which in turn generates alaser-induced pressure wave and/or vapor bubbles that produce additionalpressure waves, thereby converting the laser-induced pressure waves tomechanical energy via moving the tip 880 and/or transferring thepressure to the vascular occlusion through the tip 880.

Referring to the flow chart in FIG. 9, the present disclosure includes amethod 900 for treating a subject with a vascular occlusion usingembodiments of the catheter assemblies and systems described herein.Although it is not illustrated in FIG. 9, it may be desirable to treatat least a portion of the vascular occlusion in the vessel of thesubject prior to performing the method set forth in FIG. 9. Suchtreatment may include, for example, mechanically cutting and/or ablating(via application of laser light energy, microwave energy, radiofrequencyenergy, or the like) at least a portion of the vascular occlusion. Themethod 900 in FIG. 9 begins at block 910 by positioning an embodiment ofa catheter assembly or system described herein within the vasculature ofa subject. At block 920, the distal tip of the catheter assembly orsystem is positioned adjacent the occlusion within the vasculature (forexample, by advancing the distal tip through the vasculature). At block930, a liquid medium, such as any of the liquid mediums describedherein, is introduced to cavity at and/or proximal the distal tip of thecatheter assembly or system (for example, introduced via a space betweenan outer sheath and a laser catheter carried within the sheath). Atblock 940, laser light energy is delivered to one or more emitters (forexample, optical fibers) located within the cavity to transmit pulses oflight energy into the liquid medium. As described herein, transmissionof pulses of light energy into the liquid medium creates a laser-inducedpressure wave and/or vapor bubbles and additional resultant pressurewaves to disrupt the vascular occlusion. At block 950, the catheter (andthe emitters) may be translated relative to the sheath while laser lightenergy is delivered to one or more emitters and the liquid medium. Thecatheter (and the emitters) or the entire catheter assembly can berepositioned within the vasculature. The method 900 also includes endingthe procedure when the desired therapeutic outcome is obtained, orrepeating any of blocks 910 through 960 as may be necessary to treat asubject having a vascular occlusion. Furthermore, although it is notillustrated in FIG. 9, after performing the method 900 it may bedesirable to use a drug eluting (coated) balloon (DEB or DCB) catheterto deliver drugs to the remnants of the vascular occlusion. Disruptingthe vascular occlusion with the laser-induced pressure waves prior toutilizing a DEB may increase the effectiveness of the drugs beingapplied to the vascular occlusion because the laser-induced pressurewaves disrupt the intraluminal calcium as well as calcium within thetissue (e.g., calcium deposits and/or medial calcium) of the bloodvessel, vascular obstructions or restrictions, thereby creating apathway for the drug to enter the intraluminal and tissue portions ofthe vasculature and/or vascular occlusion.

Referring to FIG. 10, there is depicted a laser catheter 1010 and aguidewire 1020 extending through the lumen of the catheter 1010. Thelaser catheter 1010 includes one or more layers of a plurality ofoptical fibers 1016 surrounding a lumen extending therethrough, and asheath 1012 surrounds the layer(s) of optical fibers 1016. The distalend of the laser catheter 1010 may include a metal band 1014, whichimproves the strength of the distal end and provides a radiopaquemarker. Examples of laser catheters 1010 or laser sheaths are sold byThe Spectranetics Corporation under the tradenames ELCA™ and TurboElite™ (each of which is used for coronary intervention orcatheterization such as recanalizing occluded arteries, changing lesionmorphology, and facilitating stent placement) and SLSII™ and GlideLight™(which is used for surgically implanted lead removal). Again, asillustrated in FIG. 10, the working (distal) end of a laser cathetertypically has a plurality of laser emitters that emit energy and ablatethe targeted tissue. The opposite (proximal) end of a laser catheter,which is not shown, typically has a fiber optic coupler that connects toa laser system or generator. One such example of a laser system is theCVX-300 Excimer Laser System, which is also sold by The SpectraneticsCorporation.

Again, the present disclosure envisions a two-piece catheter system orkit. Referring to FIG. 11A, the system 1110 may include a laser catheter1010 radially disposed within a sheath 1140. The system may optionallyinclude a guidewire 1130 disposed within a lumen of the laser catheter1010. As discussed above, a liquid medium is introduced into the sheath1120 distal to the laser catheter 1010, particularly distal to theoptical fibers/emitters of the laser catheter 1010 such that when thelaser is activated, the liquid absorbs the light and createslaser-induced pressure waves and/or vapor bubbles and additionalresultant pressure waves and/or cavitation events. Although the liquidis not shown in this figure, the liquid may be introduced through alumen in the laser catheter 1010, a lumen in the sheath 1120 and/or thelumen or space between the laser catheter 1010 and the sheath 1120.Regardless of which of these locations is used, one or more liquidmedium ports located at or toward the proximal end of the cathetersystem will be also be used.

Referring to FIG. 12, there is depicted a representative flow diagram ofa method 1200 of removing restriction vascular occlusion using a lasercatheter 1010 to ablate a portion of the vascular occlusion, and/orusing the laser catheter 1010 in conjunction with the sheath 1120 tocreate laser-induced pressure waves in the presence of a liquid mediumand disrupt a portion of the vascular occlusion. The method 1200 mayinclude the step 1205 of positioning a guidewire 1130 within thevasculature 1140 of a subject, the step 1210 of positioning a lasercatheter 1010 over the guidewire 1130 within the vasculature 1215, thestep of positioning a sheath 1120 over the laser catheter 1010 withinthe vasculature and the step 1220 of positioning the sheath 1120 andlaser catheter 1010 (and optionally the guidewire 1130) adjacentrestriction vascular occlusion 1150 within the vasculature 1140 of asubject. Referring again to FIG. 11A, positioning the sheath 1120 andlaser catheter 1010 adjacent the vascular occlusion 1150 creates acavity for the liquid medium to collect distally of the laser catheter1010, particularly distally of the emitters/optical fibers of the lasercatheter 1010.

FIG. 11A depicts the distal end of the laser catheter 1010 proximal ofthe distal end of the sheath 1120. However, it is envisioned that thedistal end of the laser catheter 1010 may be disposed at or distally ofthe distal end of the sheath 1120, as long as there is liquid mediumbetween the emitters/optical fibers of the laser catheter 1010 and thevascular occlusion 1150. The axial locations of the laser catheter 1010and the sheath 1120 may be adjusted by translating either or bothcomponents with respect to one another. In order to visualize therespective locations of the laser catheter 1010 and the sheath 1120under fluoroscopy, the laser catheter 1010 and the sheath 1120 mayinclude radiopaque markers at any corresponding locations along theirlengths.

Continuing to refer to FIG. 11A, once the sheath 1120 and laser catheter1010 are disposed adjacent the vascular occlusion 1150, the liquidmedium may be introduced to the distal end of the laser catheter as setforth in step 1225 of FIG. 12. Continuing to refer to FIG. 12, step 1230includes activating the laser to create laser-induced pressure waves inthe presence of the liquid medium and disrupting a portion of thevascular occlusion, particularly the calcified cap of the vascularocclusion. The laser catheter 1010 and sheath 1120 may be used totraverse the entire vascular occlusion 1150, as set forth in step 1240of FIG. 12 (and optionally step 1235 of FIG. 12), or only disrupt aportion of the vascular occlusion 1150. If the laser catheter 1010 andsheath 1120 are only used to disrupt a portion of the vascular occlusion1150, then the guidewire 1130 may penetrate and traverse the vascularocclusion 1150. For example, FIG. 11B depicts the guidewire 1130penetrating and traversing the vascular occlusion 1150.

Referring to FIG. 11C, assuming that the laser catheter 1010 and sheath1120 are only used to disrupt a portion of the vascular occlusion 1150′,the laser catheter 1120 may be used to traverse the vascular occlusion1150 without the sheath 1120. Referring to step 1245 of FIG. 12, theinsertion of the liquid medium may be discontinued and the lasercatheter 1010 may be used to ablate the vascular occlusion as the lasercatheter 1150 passes over the guidewire 1130 through the vascularocclusion 1150′ while the sheath 1120 remains proximal of the vascularocclusion.

Once the entire vascular occlusion has been traversed by the lasercatheter 1010, the opening created by the laser catheter 1010 should belarge enough to translate the sheath 1120 distally and through thevascular occlusion. At this point, both the distal end of the sheath1120 and the distal end of the laser catheter 1010 should be distal ofthe vascular occlusion. At this point, referring to FIG. 11D, the lasercatheter 1010 is able to translate proximally while the sheath 1120remains stationary within the vascular occlusion. Upon introducing theliquid medium into the sheath 1120 in front of the laser catheter 1010,the laser may be activated, thereby creating laser-induced pressurewaves in the presence of the liquid medium. At least a portion of thelaser-induced pressure waves are directed radially, and as the lasercatheter 1010 translates proximally within the sheath 1120, thelaser-induced pressure waves transmit through the sheath 1120 therebydisrupting the remainder of the vascular occlusion 1150′″.

To ensure that the majority of the remainder of the vascular occlusion1150′″ is disrupted, and if desired, disrupt the intraluminal calciumand/or calcium within the tissue layers (e.g., medial layer) of theblood vessel, and the vascular occlusion, the laser catheter 1010 may berepeatedly translated distally and proximally within the sheath 1120. Asdiscussed above, disruption of the intraluminal layer and/or tissuelayers (e.g., medial layer) of the blood vessel and the vascularocclusion, can improve the vasculature's ability to absorb drugs,particularly when such drugs are applied with a drug eluting balloon.Also, it is contemplated that prior to, during and/or after any step inthe process outlined in FIG. 12, the laser catheter 1010 may be usedindividually to ablate a portion of the vascular occlusion, or the lasercatheter 1010 may be used in conjunction with the sheath 1120.

FIGS. 11A-11D illustrate the catheter system as having a sheath 1120with an open distal end or tip 1124. Referring to FIG. 13, the sheath1120′ may have a tip 1124 that is fully or partially closed. Forexample, if it is desirable to have a guidewire 1130 pass through thelaser catheter 1010 and the sheath 1120′, the tip 1124 will only bepartially closed, but if it is not necessary to utilize a guidewire,then the tip 1124 may be fully closed.

Similar to FIGS. 11A-11D, the laser catheter 1010 may translate distallyand/or proximally within the sheath 1120′. In order to ensure that acavity remains between the distal end of the laser catheter 1010 and theproximal end of the tip of the sheath 1120′, the sheath 1120′ mayinclude one or more internal stops 1160. The shape of the tip 1124 maybe configured similar to the tips 180 illustrated and described withrespect to FIGS. 2-6 such that the catheter system 1110′, including thelaser catheter 1010 tip 1124, is configured such that the energyproduced by the laser-induced pressure waves is captured within thecavity and the forces generated by the laser-induced pressure wavespropagate longitudinally, including in a forward (that is, parallel withthe vessel) direction, thereby increasing the tip's ability to disrupt,destroy and/or penetrate the vascular occlusion.

Referring to FIGS. 14A and 14B, a laser catheter system 1410 generallyincludes a laser catheter 1412, a guidewire 1414, a sheath 1416, and ahandle 1418 that translatably couples the laser catheter 1412 to thesheath 1416. The laser catheter 1412, the guidewire 1414, and the sheath1416 may be similar to, for example, the components of the two-piececatheter systems or kits described herein. As a specific example, thelaser catheter 1412, the guidewire 1414, and the sheath 1416 may besimilar to the components described above in connection with FIGS.11A-11D. The laser catheter 1412 is disposed within a lumen of thesheath 1416 and the handle 1418, and the laser catheter 1412 includes aproximal coupling 1420 for coupling to the handle 1418. The guidewire1414 is disposed within a lumen of the laser catheter 1412. The sheath1416 includes a proximal coupling 1422 for coupling to the handle 1418.

A liquid medium is introduced into the sheath 1416 distal to the lasercatheter 1412, particularly distal to the optical fibers/emitters of thelaser catheter 1412 such that when the laser is activated, the liquidabsorbs the light and creates laser-induced pressure waves and/or vaporbubbles and resultant pressure waves. The liquid is introduced via thelumen or space between the laser catheter 1412 and the sheath 1416,which in turn receives the liquid from a proximal port 1424 coupled tothe sheath 1416.

Referring now to FIGS. 14A, 14B, 15A-15G, the handle 1418 generallyincludes a base 1426 that couples to the sheath 1416 and a drivemechanism 1428 that couples to the laser catheter 1412. As described infurther detail below, a portion of the drive mechanism 1428 istranslatably coupled to the base 1426 to facilitate translating thelaser catheter 1412 within the lumen of the sheath 1416 (for example, tothe various positions shown in FIGS. 11A-11D). The drive mechanism 1428may be translated to a proximal position relative to the base 1426 (seeFIGS. 15A-15C), a distal position relative to the base 1426 (see FIGS.15E and 15F), and an infinite number of intermediate positionstherebetween (see FIGS. 15D and 15G). As a result, the laser catheter1412 may be translated to corresponding positions relative to the sheath1416.

Referring now to FIGS. 14A-17, the base 1426 includes an elongated,hollow frame 1430 that movably couples to the drive mechanism 1428. Theframe 1430 includes a proximal portion 1432, an intermediate portion1434, and a distal portion 1436. The proximal portion 1432 defines aproximal passageway 1438 for translatably receiving a shaft 1440 of thedrive mechanism 1428 therein. Referring specifically to FIGS. 16B, 16C,and 17, the proximal passageway 1438 may include a first key featurethat, by coupling to a second key feature of the shaft 1440, inhibitsrotation of the shaft 1440 relative to the frame 1430. For example, thesecond key feature of the shaft 1440 may be a non-circularcross-sectional area, and the first key feature of the proximalpassageway 1438 may be a cross-sectional area that is approximatelyidentical (that is, permitting sufficient clearance to permit relativelongitudinal translation, but inhibit relative rotation and transversetranslation) to the cross-sectional area of the shaft 1440, or across-sectional area that is approximately identical to a portion of thecross-sectional area of the shaft 1440. As a more specific example andas shown in FIGS. 16B, 16C, and 17, the shaft 1440 includesrectangle-like cross-sectional shape, with two opposing flat sidesurfaces 1442 and two opposing arcuate side surfaces 1444. The proximalpassageway 1438 includes a cross-sectional area that is approximatelyidentical to a portion of the cross-sectional area of the shaft 1440.Specifically, the proximal passageway 1438 is defined by four opposingflat side surfaces 1446 and two opposing arcuate side surfaces 1448. Theflat side surfaces 1446 and the arcuate side surfaces 1448 engage theflat side surfaces 1442 and the arcuate side surfaces 1444 of the shaft1440, respectively, to permit relative longitudinal translation, butinhibit relative rotation and transverse translation of the shaft 1440relative to the frame 1430. In the present example, the proximalpassageway 1438 is also defined by two additional opposing arcuate sidesurfaces 1449 that extend between the flat side surfaces 1446. Thearcuate side surfaces 1449 are disposed apart from the shaft 1440 toreduce sliding friction between the shaft 1440 and the frame 1430.

Referring specifically to FIGS. 16A, 16D, and 16E, the intermediateportion 1434 of the frame 1430 includes a first bearing portion 1450, asecond bearing portion 1452, and an opening 1454 extending therebetweenand aligned with the proximal passageway 1438. Each of the first andsecond bearing portions 1450, 1452 includes first and second bearingsurfaces 1456, 1458. The first and second bearing surfaces 1456, 1458rotatably support a control element 1460 of the drive mechanism 1428.Each of the first and second bearing portions 1450, 1452 also includes aclearance surface 1462 between the bearing surfaces 1456, 1458. Theclearance surface 1462 is also disposed radially inwardly relative tothe bearing surfaces 1456, 1458. The clearance surface 1462, togetherwith the opening 1454, facilitates driving engagement of the controlelement 1460 with the shaft 1440, as described in further detail below.Within the opening 1454, each of the first and second bearing portions1450, 1452 includes a guide surface 1464. The guide surface 1464 stranslatably couple to the shaft 1440 and inhibit the shaft 1440 fromrotating within the frame 1430.

Referring briefly to FIGS. 15H-15J, to facilitate assembly of the base1426, each clearance surface 1462 may be monolithically coupled with thefirst bearing surface 1456, 1458. After positioning the shaft 1440within the frame 1430 and the control element 1460 over the firstbearing surface 1456, 1458 and the clearance surface 1462, eachclearance surface 1462 may couple to the second bearing surface 1456,1458 via, for example, press fit, one or more adhesives, snap connectors(not shown), or the like.

Referring to FIGS. 16A, 16F, and 16G, the distal portion 1436 of theframe 1430 may be similar to the proximal portion 1432 of the frame1430. That is, the distal portion 1436 defines a distal passageway 1466aligned with the opening 1454 for translatably receiving the shaft 1440.Referring specifically to FIGS. 16F, 16G, and 17 and in a similar mannerto the proximal passageway 1438, the distal passageway 1466 may includea first key feature that, by coupling to the second key feature of theshaft 1440, inhibits rotation of the shaft 1440 relative to the frame1430. For example, the second key feature of the shaft 1440 may be anon-circular cross-sectional area, and the first key feature of thedistal passageway 1466 may be a cross-sectional area that isapproximately identical to the cross-sectional area of the shaft 1440,or a cross-sectional area that is approximately identical to a portionof the cross-sectional area of the shaft 1440. In accordance with thespecific example described above and as shown in FIGS. 16F, 16G, and 17,the distal passageway 1466 includes a cross-sectional area that isapproximately identical to a portion of the cross-sectional area of theshaft 1440. Specifically, the distal passageway 1466 is defined by fouropposing flat side surfaces 1468 and two opposing arcuate side surfaces1470. The flat side surfaces 1468 and the arcuate side surfaces 1470engage the flat side surfaces 1442 and the arcuate side surfaces 1444 ofthe shaft 1440, respectively, to permit relative longitudinaltranslation, but inhibit relative rotation and transverse translation ofthe shaft 1440 relative to the frame 1430. In the present example, thedistal passageway 1466 is also defined by two additional opposingarcuate side surfaces 1472 that extend between the flat side surfaces1468. The arcuate side surfaces 1472 are disposed apart from the shaft1440 to reduce sliding friction between the shaft 1440 and the frame1430.

Referring again to FIGS. 14A-16G, at its proximal end, the frame 1430couples to a proximal cover 1476 (for example, via press fit, one ormore adhesives, or the like). The proximal cover 1476 includes aproximal aperture 1478 (see FIGS. 15F and 15G) for permitting the lasercatheter 1412 to extend into the frame 1430. At its distal end, theframe 1430 couples to a distal cover 1480 (for example, via press fit,one or more adhesives, or the like). The distal cover 1480 includes adistal aperture 1482 (see FIGS. 15F and 15G) for permitting the lasercatheter 1412 to extend out of the frame 1430 and into the sheath 1416.The distal aperture 1482 press-fittingly receives a tube 1484 (forexample, a hypotube 1484) that extends into the shaft 1440 and receivesthe laser catheter 1412. The distal aperture 1482 also press-fittinglyreceives a distal coupling 1486 that detachably and sealingly couples tothe proximal coupling 1422 of the sheath 1416.

Referring now to FIGS. 14A and 15A-15J, the drive mechanism 1428generally includes the shaft 1440 and the control element 1460.Referring specifically to FIGS. 15F-15J, the shaft 1440 includes a shaft1440 passageway 1488 for permitting the laser catheter 1412 to extendthrough the shaft 1440 and for receiving the tube 1484. The shaft 1440passageway 1488 press-fittingly receives a proximal coupling 1490 thatdetachably and sealingly couples to the proximal coupling 1420 of thelaser catheter 1412. As such, movement of the control element 1460relative to the base 1426 causes the shaft 1440 to translate within thebase 1426, the laser catheter 1412 thereby translates within the lumenof the sheath 1416.

The shaft 1440 passageway 1488 also receives a seal 1492, for example,an O-ring that translatably engages the outer surface of the tube 1484.As such, the seal 1492 inhibits the liquid in the shaft 1440 passageway1488 (received from the sheath 1416 via the distal coupling 1486 and thehypotube 1484) from exiting the shaft 1440 by flowing between the shaft1440 and the tube 1484.

As described briefly above, the control element 1460 is rotatablysupported by the frame 1430. The control element 1460 includes a firstengagement feature that couples to a second engagement feature of theshaft 1440 such that rotation of the control element 1460 relative tothe base 1426 causes translation of the shaft 1440 relative the base1426 (and translation of the laser catheter 1412 within the lumen of thesheath 1416). For example and as shown in the Figures, the firstengagement feature may be a first threaded surface 1494 within thecontrol element 1460, and the second engagement feature may be a secondthreaded surface 1496 formed on the arcuate side surfaces 1444 of theshaft 1440. Stated differently, the shaft 1440 may include a second,interrupted threaded surface that extends from the opening 1454 in theframe 1430 to engage the first threaded surface 1494 of the controlelement 1460. In any case, rotation of the control element 1460 and thefirst threaded surface 1494, together with the shaft 1440 beingrotatably fixed within the frame 1430, causes translation of the secondthreaded surface 1496 and the shaft 1440 relative to the frame 1430 (andtranslation of the laser catheter 1412 within the lumen of the sheath1416).

Laser-induced pressure waves generally have different characteristics incomparison to ultrasound. Ultrasound typically consists of periodicoscillations with limited bandwidth. Laser-induced pressure waves aresingle, mainly positive pressure pulses that are followed bycomparatively small tensile wave components. Ultrasound applies analternating high frequency load to tissue, with a frequency range ofseveral megahertz, and can thus lead to heating, tissue tears andcavitation at high amplitudes. The effect of laser-induced pressurewaves in comparison, however, largely involves radially directed energy,as described above, enabling the treatment of deep tissue as well asadjacent tissue with enhanced sensitivity.

The ability of the catheter of the present disclosure to generatelaser-induced pressure waves for treating a vascular occlusion in asubject involves the suitable coupling of the light system and theliquid medium. Any wavelength of light can be used, including but notlimited to, laser light, visible light, ultraviolet light and infraredlight, as long as the light being emitted is coupled with a liquidmedium capable of absorbing the light and producing laser-inducedpressure waves. Additionally, any liquid medium can be used, as long asthe liquid medium is coupled with a light source that emits light at asuitable wavelength such that the liquid absorbs the light and createslaser-induced pressure waves and/or vapor bubbles. In some cases, theliquid medium can be contrast medium (for example, iodine-containingcontrast medium or gadolinium contrast medium) and/or the liquid mediumcan be a contrast solution comprising a biocompatible fluid (forexample, saline) in which a contrast dye(s) or particle(s) have beenmixed at various concentrations.

The force amplitude generated by the laser-induced pressure wavesdepends in part on the degree of absorption of the light energy by theliquid medium as well as total energy deposited by the light source.Generally, the greater the absorption of the light energy by the liquidmedium 160, the greater the force generated by the laser-inducedpressure waves. Also, the greater the amount of the light energydelivered to the liquid medium 160, the greater the force generated bythe laser-induced pressure waves. For example, an excimer lasertypically emits laser light at a wavelength of about 308 nanometers atpulse durations between about 120 nanoseconds and about 140 nanoseconds,at frequencies between about 25 pulses per second to about 80 pulses persecond, and with a total energy output between about 1 to about 100millijoules. In some cases, however, total energy output of a laserlight system can range from greater than 0 to about 300 mJ. When emittedwithin contrast medium, such as iodine-containing contrast medium orgadolinium contrast medium, there will be a very high degree ofabsorption by the contrast medium, thus creating laser-induced pressurewaves with sufficient force to treat a vascular occlusion in a subject.

Light energy can be emitted at any suitable wavelength capable ofgenerating laser-induced pressure waves. Light energy can be emittedbetween about 1 nanometer and about 1 millimeter. In some cases, lightcan be emitted from about 10 nanometers to about 5000 nanometers. Insome cases, light can be emitted from about 100 nanometers to about 1000nanometers. In some cases, light can be emitted from about 250nanometers to about 750 nanometers. In some cases, light can be emittedfrom about 300 nanometers to about 600 nanometers. In still other cases,light can be emitted from about 300 nanometers to about 350 nanometers.

Light energy can be emitted at any suitable pulse duration capable ofgenerating laser-induced pressure waves. In some cases, light can beemitted at pulse durations between about 1 femtosecond to about 1second. In some cases, light can be emitted at pulse durations betweenabout 10 nanoseconds to about 500 nanoseconds. In some cases, light canbe emitted at pulse durations between about 100 nanoseconds to about 150nanoseconds. In still other cases, light can be emitted at pulsedurations between about 120 nanoseconds and about 140 nanoseconds.

Light energy can be emitted at any suitable pulse repetition frequency(PRF), or pulses per second, capable of generating vapor bubbles andproducing resultant pressure waves that propagate through thesurrounding vasculature. In some cases, light can be pulsed at afrequency of between about 1 pulse to about 5000 pulses per second. Insome cases, light can be pulsed at a frequency of between about 10pulses to about 2500 pulses per second. In some cases, light can bepulsed at a frequency of between about 10 pulses to about 1500 pulsesper second. In some cases, light can be pulsed at a frequency of betweenabout 100 pulses to about 1000 pulses per second. In other cases, lightcan be pulsed at a frequency of between about 50 pulses to about 500pulses per second. In other cases, light can be pulsed at a frequency ofbetween about 50 pulses to about 150 pulses per second. In other cases,light can be pulsed at a frequency of between about 50 pulses to about100 pulses per second. In still other cases, light can be pulsed at afrequency of between about 25 pulses to about 80 pulses per second.

The total number of pulses administered during a particular treatmentperiod depends on a variety of factors, including patientcharacteristics, the type of condition being treated, and the specificcharacteristics of the vascular occlusion, as one of ordinary skill inthe art would readily appreciate based on the present disclosure. Insome cases, the total number of pulses administered during a treatmentperiod can range from a single pulse to any number of pulses generatedin a 10 second treatment period, a 15 second treatment period, a 20second treatment period, a 25 second treatment period, a 30 secondtreatment period, up to a 1 minute treatment period. Treatment periodscan be repeated depending on the extent of the vascular occlusionremaining after initial treatment.

For example, a generator and/or one or more emitters may be configuredto emit laser light energy at wavelengths of between about 150nanometers to about 400 nanometers, at pulse durations between about 1femtosecond to about 1 second, and at frequencies between about 1 pulseper second to about 5000 pulses per second. In some cases, the generatorand/or the emitter(s) may be configured to emit laser light energy atwavelengths of between about 400 nanometers to about 800 nanometers, atpulse durations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond. In other cases, the generator and/or the emitter(s) may beconfigured to emit laser light energy at wavelengths of between about800 nanometers to about 3,000 nanometers, at pulse durations betweenabout 1 femtosecond to about 1 second, and at frequencies between about1 pulse per second to about 5000 pulses per second. In other cases, thegenerator and/or the emitter(s) may be configured to emit laser lightenergy at wavelengths of between about 3,000 nanometers to about 12,000nanometers, at pulse durations between about 1 femtosecond to about 1second, and at frequencies between about 1 pulse per second to about5000 pulses per second. In other cases, the generator and/or theemitter(s) may be configured to emit laser light energy at wavelengthsof between about 300 nanometers to about 360 nanometers, at pulsedurations between about 1 femtosecond to about 1 second, and atfrequencies between about 1 pulse per second to about 5000 pulses persecond.

The degree of force generated by the laser-induced pressure waves can bemodulated by using lasers that produces laser light energy at differentwavelengths and at different pulse durations, as would be appreciated byone of ordinary skill in the art based on the present disclosure. Forexample, different degrees of force may be required to break apart avascular occlusion, as compared to the degree of force required todeliver a therapeutic agent to vascular tissue. In some embodiments, alaser having a holmium source, referred a Holmium laser, can emit laserlight energy at a wavelength of about 2,100 nanometers (nm) and can becoupled with various light absorbing materials, including an aqueous orsaline-based medium, to treat a vascular occlusion in a subject.

Several other additional sources of laser light energy can be pairedwith corresponding light absorbing materials to generate laser-inducedpressure waves to treat a vascular occlusion. For example, YAG crystallasers can produce wavelengths of infrared light, which is highlyabsorptive in aqueous solutions. Aqueous solutions can be used as lightabsorbing material or medium to generate laser-induced pressure waves.Aqueous solutions include, but are not limited to, saline, dextrose,radio-opaque contrast, lactated ringer's, and electrolyte solutions. Insome cases, YAG wavelengths can be doubled to generate visible spectrumlight of 532 nm wavelength. Materials or medium capable of absorbinglight of this wavelength include, but are not limited to, goldnanospheres, nitrite solutions, potassium permanganate solutions, coppersalts, aluminum solutions, aluminon, ammonia salts, and dyes such ashemotoxylin and propidium iodide. Light absorbing materials such asthese can be part of a solution, such as an aqueous solution asdescribed above, and/or they can be applied as coatings on varioussurfaces within a device.

In some embodiments, a Holmium YAG laser can emit laser light energy ata wavelength of about 2,120 nm and can be coupled with various lightabsorbing materials, including an aqueous or saline-based medium, totreat a vascular occlusion in a subject. In some embodiments, a thuliumlaser, such as a Thulium YAG laser, can emit laser light energy at awavelength of about 2,013 nm and can be coupled with various lightabsorbing materials, including an aqueous or saline-based medium, totreat a vascular occlusion in a subject. In some embodiments, a thuliumlaser, such as a Thulium Fiber laser, can emit laser light energy at awavelength of about 1,908 nm and can be coupled with various lightabsorbing materials, including an aqueous or saline-based medium, totreat a vascular occlusion in a subject. In some embodiments, an Nd-YAGlaser can emit laser light energy at a wavelength of about 1,064 nm andcan be coupled with various light absorbing materials to treat avascular occlusion in a subject. In some embodiments, a doubled YAGlaser can emit laser light energy at a wavelength of about 532 nm andcan be coupled with various light absorbing materials to treat avascular occlusion in a subject. In some embodiments, an alternativeband YAG laser can emit laser light energy at a wavelength of about1,319 nm and can be coupled with various light absorbing materials totreat a vascular occlusion in a subject. In still other embodiments, anEr-YAG laser can emit laser light energy at a wavelength of about 2,940nm and can be coupled with various light absorbing materials to treat avascular occlusion in a subject.

Carbon dioxide (CO₂) lasers can emit infrared light that is highlyabsorptive in aqueous solutions. CO₂ lasers are common surgical lasersand are highly absorptive in tissues due to their high water content.Light absorbing materials that can be coupled with CO₂ lasers that emitinfrared light, such as light emitted at a 10.6 micron wavelength, togenerate laser-induced pressure waves include, but are not limited to,aqueous solutions such as saline, dextrose, radio-opaque contrast,lactated ringer's, and electrolyte solutions.

Nitrogen lasers can be used to produce low frequency, high energy laserpulses. Nitrogen lasers can emit light in the UV spectrum can emit laserlight energy at a wavelength of about 337 nm and can be coupled withvarious light absorbing materials to generate laser-induced pressurewaves, including but not limited to, radio-opaque contrast as well asmetals and oxides such as aluminum, silver, gold, copper, nickel,cerium, zinc, titanium, and dyes such as hydroxycoumarin andaminocoumarin.

Other medically useful lasers that can be used to generate alaser-induced pressure wave to treat a vascular occlusion includeTi-Sapphire lasers, which can emit laser light energy at wavelengths ofabout 800 nm; Ruby lasers, which can emit laser light energy atwavelengths of about 694 nm; and Alexandrite lasers, which can emitlaser light energy at about 755 nm. These medical lasers emit laserlight energy in the near infrared light spectrum, and can be used forlaser-induced pressure wave generation. Light absorbing material ormedium that can be coupled with these laser include, but are not limitedto, dyes and colorants which could be used in solution, suspension, orcoating on another material or surface within a device. Variousmaterials capable of absorbing laser light energy in these wavelengthsinclude aqueous copper, copper salts, and cupric sulfate, and materialssuch as fluorophores that are used in fluorescent microscopy (forexample, methylene blue).

Dye lasers can also be used to generate laser-induced pressure waves totreat a vascular occlusion. In some cases, dye lasers can be tuned tooutput a specific wavelength of light in the visible spectrum, which canallow for the optimization of the laser for a certain light absorbingmaterial, as an alternative or in addition to, using a material which ishighly absorptive of a specific wavelength of light. In this way, thelight absorbing material can be any of the previously mentionedmaterials, as well as dyes, colorants, and visible light chromophores.

For certain applications, it may be desirable to increase the amountand/or the size of vapor bubbles produced along with a laser-inducedpressure wave that is generated by emitting laser light energy into acorresponding light absorbing liquid medium. For example, when enteringsmaller diameter sized blood vessels, the size of the catheter may belimited. In some cases, the force that vapor bubbles exert on tissue(for example, a vascular occlusion) may be proportional to the size ofthe individual vapor bubbles created, as the bubbles expand and contractafter laser light energy is emitted into liquid medium and a pressurewave is generated. That is, the strength of the initial laser-inducedpressure wave and/or the size of the vapor bubble may be limited withthe use of a non-gas saturated liquid medium. One manner by which thesize of individual vapor bubbles can be increased (for example, toimpart greater amount of force on a particular tissue) is to saturatethe liquid medium with gaseous substances so that the gas within theliquid medium exhibits a higher vapor pressure as compared to that ofthe liquid medium without such gas. Suitable gaseous substances that maybe used to create gas-saturated liquid medium include, but are notlimited to, ambient air, carbon dioxide, iodine gas, oxygen, nitrogen,compressed air, nitrous oxide, and combinations of these.

The higher vapor pressure of the gaseous substance added to the liquidmedium will cause the gaseous substance to return to a gaseous statefaster (under smaller pressure fluctuations) than the liquid medium. Inother words, less pressure is required to cause the saturated gaseoussubstances to come out of solution, resulting in the creation of largervapor bubbles, and concomitantly, a greater amount of force. In somecases, the use of gas-saturated liquid medium allows for the use oflaser light energy at decreased intensities, or decreased pulses orpulse durations, without any accompanying decrease in the overall forcegenerated by the vapor bubbles (as each vapor bubble is larger). Thiscan enhance both the safety and efficacy of the procedure beingperformed.

The gaseous substances can be imparted to the liquid medium throughvarious means, including under pressure, through mechanical agitation,and/or by bubbling the gas into the liquid medium. In some cases,gas-saturated liquid medium can be prepared prior to a procedure andthen delivered to the distal end of a catheter prior to performing theprocedure. Additionally or alternatively, gaseous substances can bedelivered into that liquid medium that is already present in thecatheter.

The gases and/or gaseous substances may be dissolved and quantified bythe amount of gases present in a 1 kg of the liquid medium. The maximumamount of gas that will dissolve in the liquid medium is dependent onthe solubility of the particular gas in that liquid medium, thepressure, and the temperature as described by Henry's law of gassolubility. For example, carbon dioxide may be dissolved into water at aconcentration of 1.25 g/kg of water or less at 30 degrees C. underatmospheric pressure. And upon dissolving carbon dioxide into water orsaline, an overall concentration between 0.25-3.5 g/kgH₂O is produced.The concentrations of other dissolved gases in a kilogram of liquidmedium ranges from 1 mg-1 g/kg for iodine, 5-80 mg/kg for oxygen, 5-40mg/kg for nitrogen, 5-500 mg/kg for room air, and 0.1-4 g/kg for nitrousoxide.

The gases and/or gaseous substances may be dissolved in quantities abovethe theoretical limit, which is known as super saturation. Thetheoretical limit is described by Henry's law as mentioned previously.By dissolving the gases under increased pressure or decreasedtemperature and then returning it to normal atmospheric conditions, itis possible to dissolve a larger quantity of gas then is possible atatmospheric conditions. For example, 2.5 g of carbon dioxide may bedissolved into 30 degrees C. water under 2 atm of pressure, and thenreturned to atmospheric pressure. For any dissolved gas, the saturationpercentage is defined by the concentration of gas over the theoreticalmaximum concentration. For any of the previously mentioned gases in asupersaturated solution, the saturation percentage can range from100-300 percent.

The use of a gas saturated liquid medium or super saturated liquidmedium may also increase the initial laser-induced pressure wave causedby the interaction of the laser light and the liquid medium. That is,the gas saturated liquid medium or super saturated liquid medium maycontain larger potential energy, which when activated by the laserlight, may create a larger initial laser-induced pressure wave incomparison to a laser-induced pressure wave created by the interactionof laser light and a non-gas saturated liquid medium.

Additionally or alternatively, methods of the present disclosure alsoinclude activating at least one proximal laser emitter enclosed withinthe sheath assembly to send pulses of laser light energy through theliquid medium and propagating laser-induced pressure waves to assist instent deployment. Pressure waves generated from vapor bubbles can assistin seating or expanding the stent to its full diameter as part of amedical procedure.

As discussed above, activating one or more emitters and transmittingpulses of light energy into the liquid medium produces vapor bubbles.Upon emitting light from an emitter, such as a laser catheter, within asheath that contains an absorptive liquid medium, the vapor bubbles maybe produced within the interior of the sheath and/or exterior to thesheath. Assuming that the vapor bubbles are created on the interior ofthe sheath, it may be desirable to limit some or all of the potentialexpansion of the relevant portion of the sheath caused by the vaporbubbles. That is, it may be desirable to reduce or prevent the sheath'sability to expand and contract upon creation of the vapor bubblestherein so as to reduce or prevent the sheath from applying a hydraulicforce or pressure to the vascular occlusion and/or to the walls of thevessel. Also, assuming that the vapor bubbles are created on exterior ofthe sheath within the vessel wall, it may be desirable to reduce and/orprevent the formation of such vapor bubbles so as to reduce or preventthe cavitation event and the formation of the vapor bubbles themselvesfrom applying a hydraulic force or pressure to the vascular occlusionand/or to the walls of the vessel.

Referring to FIG. 18, there is depicted a perspective view ofbiocompatible sheath 1120″ that can be used in conjunction with a lasercatheter or any of the earlier embodiments to perform a method oftreating a subject, such as removing or treating a vascular occlusion.The sheath 1120″ may include a sleeve or jacket 1122″ and an attenuatingmember 1124″. FIG. 18 illustrates the attenuating member 1124″ as beingexposed and coupled to the distal end of the sleeve 1122″ via anadhesive. The attenuating member 1124″, however, can alternatively beintegrally disposed within the sleeve 1122″, disposed on the exterior ofthe sleeve 1122″ and/or disposed on the interior of the sleeve 1122″.Additionally, if the attenuating member 1124″ is coupled to the distalend of the sleeve 1122″ or the attenuating member 1124″ is integrallydisposed within the sleeve 1122″ or disposed on the interior of thesleeve 1122″, the entire attenuating member 1124″ may be covered(unexposed) by the sleeve 1122″, the entire attenuating member 1124″ maybe exposed, or a portion (for example, distal portion) of theattenuating member 1124″ may be exposed and another portion (forexample, proximal portion) may be covered.

FIG. 18 also illustrates the attenuating member 1124″ as being disposedat the distal end of the sheath 1120″. The attenuating member 1124″,however, may alternatively and/or additionally as be disposed at theproximal end of the sheath 1120″, the central portion of the sheath1120″, any location or multiple locations between the proximal end anddistal end of the sheath 1120″, or in the entire length or substantiallythe entire length of the sheath 1120″.

The attenuating member 1124″ has two purposes. One purpose is toreinforce the sleeve 1122″ and/or the sheath 1120″, and the otherpurpose is to reduce the size or prevent the likelihood formation ofvapor bubbles exterior of the attenuating member 1124″, the sleeve 1122″and/or the sheath 1120″. Regarding the reinforcing the sleeve 1122″,coupling the attenuating member 1124″ with the sleeve 1122″ may reduceor prevent the sheath's ability to expand and contract upon creation ofthe vapor bubbles therein so as to reduce or prevent the sleeve 1122″from applying a hydraulic force or pressure to the vascular occlusionand/or to the walls of the vessel. Reinforcing the sleeve 1122″ mayminimize and/or prevent the sleeve from bulging, splitting, ordelaminating (in the event the sleeve comprises multiple layers), aswell as minimize and/or prevent a hole from forming within the sleeve.In the event of one or more occurrences, the difficulty of subsequenttranslation of the sleeve through the patient's vasculature and/ortranslation relative to the laser catheter may be increased.

Both the attenuating member 1124″ and the sleeve 1122″ are constructedof biocompatible materials. Coupling the attenuating member 1124″ withthe sleeve 1122″ forms a rigid or semi-rigid structure within the sheath1120″ such that it applies a small hydraulic force or it does not applya hydraulic force to the vascular occlusion and/or to the walls of thevessel upon formation of vapor bubbles therein. It may be desirable thatthe majority or only force(s) applied to the vascular occlusion and/orto the walls of the vessel are a result of the laser-induced pressurewaves that pass through the 1120″, thereby allowing more precise controlover the laser-induced pressure waves.

Regarding the other purpose of the attenuating member 1124″, which is toreduce or prevent the formation of vapor bubbles exterior of theattenuating member 1124″, the sleeve 1122″ and/or the sheath 1120″ andcontinuing to refer to FIG. 18, the openings 1126″ within theattenuating member 1124″ may prevent the formation and propagation ofvapor bubbles on the sheath 1120″. The openings 1126″ not only allow thelaser-induced pressure waves to pass therethrough, but the quantity andsize of the openings 1126″, particularly with respect to the remainderof the structural mass (or portions thereof 1128″) of the sleeve 1122″,may also limit the size of the vapor bubbles that can form on theexterior of the sheath 1120″. The relationship between the open area andthe closed area (or the ratio of the open area to the overall area)within the attenuating member 1124″ should be such that a sufficientamount of the laser-induced pressure waves pass through the attenuatingmember 1124″. And the size of the openings 1126″ should allow thelaser-induced pressure waves to pass therethrough, while also limitingthe size of the vapor bubbles that can form on the exterior of thesheath 1120″. Accordingly, it may be desirable for the ratio of the openarea to the overall area of the attenuating member 1124″ to be between 1percent-99 percent, including any increment therebetween such as 2percent, 3 percent, 4 percent, 5 percent, 6 percent, 7 percent, 8percent, 9 percent, 10 percent, . . . , 15 percent . . . 0.20 percent, .. . , 25 percent, . . . , 30 percent, . . . , 35 percent, . . . , 40percent, . . . , 45 percent, . . . , 50 percent, . . . , 55 percent, . .. , 60 percent, . . . , 65 percent, . . . , 70 percent, . . . , 75percent, . . . , 80 percent, . . . , 85 percent, . . . , 90 percent, 91percent, 92 percent, 93 percent, 94 percent, 95 percent, 96 percent, 97percent, and 98 percent. It may also be desirable for the ratio of theopen area to the overall area of the attenuating member 1124″ to bewithin a particular range such as between 5 percent to 95 percent, 10percent to 90 percent, 15 percent to 85 percent, 20 percent to 80percent, 25 percent to 75 percent, 30 percent to 70 percent, 35 percentto 65 percent, 40 percent to 60 percent, and 45 percent to 55 percent.Additionally, for any of the above listed ratios it may be desirable foreach opening to have a particular size, such as between 10 microns to10,000 microns (1 millimeter), including any increment therebetween suchas 10 microns, . . . , 12.5 microns, . . . , 15 microns, 17.5 microns, .. . 20 microns, . . . 30 microns, . . . 40 microns, . . . 50 microns, .. . 75 microns, . . . 100 microns, . . . , 125 microns, . . . , 150microns, 175 microns, . . . , 200 microns, . . . , 300 microns, . . . ,400 microns, . . . , 500 microns, . . . , 600 microns, . . . , 700microns, . . . , 800 microns, . . . , 900 microns, . . . , 1000 microns,. . . , 2000 microns, . . . , 3000 microns, . . . , 4000 microns, . . ., 5000 microns, . . . , 6000 microns, . . . , 7000 microns, . . . , 8000microns, . . . , 9000 microns, . . . , 9100 microns, . . . , 9200microns, . . . , 9300 microns, . . . , 9400 microns, . . . , 9500microns, . . . , 9600 microns, . . . , 9700 microns, . . . , 9800microns, . . . , 9900 microns, . . . , and 10,000 microns. It may alsobe desirable for the size openings 1126″ within the attenuating member1124″ to be within a particular range such as between 1000 to 9000microns, 2000 to 8000 microns, 3000 to 7000 microns, 4000 to 6000microns, and 4500 to 5500 microns.

The attenuating member's ability to reduce or prevent the formation ofvapor bubbles exterior of the attenuating member 1124″, the sleeve 1122″and/or the sheath 1120″ potentially reduces the existence and/or thesize of the vapor bubbles formed on the exterior of the attenuatingmember 1124″, the sleeve 1122″ and/or the sheath 1120″, which in turnreduces the likelihood that vapor bubbles will be created and expand andcontract between the attenuating member 1124″, the sleeve 1122″ and/orthe sheath 1120″ and the vasculature wall. And reducing or preventingexpansion and contraction of vapor bubbles between the sleeve 1122″,and/or the sheath 1120″, and the vasculature wall prevent or reduce thelikelihood that a hydraulic force or pressure will be applied to thevascular occlusion and/or to the walls of the vessel, thereby preventingand/or minimizing potential damage to the vasculature itself.

Regarding the attenuating member's ability to reinforce the sleeve 1122″and/or the sheath 1120″, the attenuating member 1124″ may reduce orprevent the sleeve's ability and/or the sheath's ability to expand andcontract upon creation of the vapor bubbles therein. Reducing thesleeve's ability and/or the sheath's ability to expand and contract uponthe formation of vapor bubbles therein, reduces or prevents the sleeve1122″ and/or the sheath 1120″ from applying a hydraulic force orpressure to the vascular occlusion, restriction and/or to the walls ofthe vessel.

The openings 1126″ in the attenuating member 1124″ depicted in FIG. 18are shown as hexagons, which are disposed around the circumference ofthe attenuating member 1124″, as well as along its length. Although theopenings 1126″ in the attenuating member 1124″ are illustrated ashexagons, the openings may have an alternate shape, such as a circle,oval, triangle, square, rectangle, helix, polygon, diamond, pentagon,heptagon, octagon, nonagon, and decagon. For example, FIG. 18Aillustrates a side view of a attenuating member 1124″ comprising aplurality of square-shaped openings; FIG. 18B is a side view of aattenuating member 1124″ comprising a plurality of diamond-shapedopenings, FIG. 18C is a side view of a attenuating member 1124″comprising a plurality of openings formed by a helical structure woundin a particular direction (for example, clockwise or left to right)while FIG. 18D is a side view of a attenuating member 1124″ comprising aplurality of openings formed by a helical structure wound in analternate direction (for example, counter-clockwise or right to left).Additionally, the two helically formed attenuating members 1124″ may becombined to form the attenuating member 1124″ depicted in FIG. 18E. Theattenuating member 1124″ depicted in FIG. 18E is similar to theattenuating member 1124″ depicted in FIG. 18B, but the attenuatingmember 1124″ depicted in FIG. 18B is braided and the attenuating member1124″ depicted in FIG. 18E is wound or formed by one or two hypotubes.Additionally, the structural mass (or portions thereof) of theattenuating member 1124″ depicted in FIG. 18E is larger than thestructural mass (or portions thereof 1128″) of the attenuating member1124″ depicted in FIG. 18B because braided materials are generallysmaller in size. Referring to FIG. 18F, the structural mass (or portionsthereof) of the attenuating member 1124″ are substantial in comparisonto the size of the hexagonal openings.

Referring to FIG. 19, there is depicted a representative flow diagram ofa method 1500 of treating a subject using a laser catheter 1010(depicted in FIG. 10) and the sheath 1120″ (depicted in FIG. 18), and/orusing the laser catheter 1010 in conjunction with the sheath 1120 toablate a vascular occlusion and/or create laser-induced pressure wavesin the presence of a liquid medium and disrupt a portion of the vascularocclusion as depicted in FIGS. 11A-11D. The method 1500 may include thestep 1505 of positioning a guidewire 1130 within the vasculature 1140 ofa subject, the step 1510 of positioning a laser catheter 1010 over theguidewire 1130 within the vasculature 1515, the step of positioning asheath 1120 over the laser catheter 1010 within the vasculature and thestep 1520 of positioning the sheath 1120 and laser catheter 1010 (andoptionally the guidewire 1130) adjacent an vascular occlusion 1150within the vasculature 1140 of a subject. Referring again to FIG. 11A,positioning the sheath 1120 and laser catheter 1010 adjacent thevascular occlusion 1150 creates a cavity for the liquid medium tocollect distally of the laser catheter 1010, particularly distally ofthe emitters/optical fibers of the laser catheter 1010.

FIG. 11A depicts the distal end of the laser catheter 1010 proximal ofthe distal end of the sheath 1120. However, it is envisioned that thedistal end of the laser catheter 1010 may be disposed at or distally ofthe distal end of the sheath 1120, as long as there is liquid mediumbetween the emitters/optical fibers of the laser catheter 1010 and thevascular occlusion 1150. The axial locations of the laser catheter 1010and the sheath 1120 may be adjusted by translating either or bothcomponents with respect to one another. In order to visualize therespective locations of the laser catheter 1010 and the sheath 1120under fluoroscopy, the laser catheter 1010 and the sheath 1120 mayinclude radiopaque markers at any corresponding locations along theirlengths.

Continuing to refer to FIG. 11A, once the sheath 1120 and laser catheter1010 are disposed adjacent the vascular occlusion 1150, the liquidmedium may be introduced to the distal end of the laser catheter as setforth in step 1525 of FIG. 19. Continuing to refer to FIG. 19, step 1530includes activating the laser to create laser-induced pressure waves inthe presence of the liquid medium and disrupting a portion of thevascular occlusion, particularly the calcified cap of the vascularocclusion. The laser catheter 1010 and sheath 1120 may be used totraverse the entire vascular occlusion 1150, as set forth in step 1540of FIG. 19 (and optionally step 1535 of FIG. 19), or only disrupt aportion of the vascular occlusion 1150. If the laser catheter 1010 andsheath 1120 are only used to disrupt a portion of the vascular occlusion1150, then the guidewire 1130 may penetrate and traverse the vascularocclusion 1150. For example, FIG. 11B depicts the guidewire 1130penetrating and traversing the vascular occlusion 1150.

Referring to FIG. 11C, assuming that the laser catheter 1010 and sheath1120 are only used to disrupt a portion of the vascular occlusion 1150′,the laser catheter 1120 may be used to traverse the vascular occlusion1150 without the sheath 1120. Referring to step 1545 of FIG. 19, theinsertion of the liquid medium may be discontinued and the lasercatheter 1010 may be used to ablate vascular occlusion as the lasercatheter 1150 passes over the guidewire 1130 through the vascularocclusion 1150′ while the sheath 1120 remains proximal of the vascularocclusion.

Referring to step 1550 of FIG. 19 and once the entire vascular occlusionhas been traversed by the laser catheter 1010, the opening created bythe laser catheter 1010 should be large enough to translate the sheath1120 distally and through the vascular occlusion. At this point, boththe distal end of the sheath 1120 and the distal end of the lasercatheter 1010 should be distally of the vascular occlusion. At thispoint, referring to FIG. 11D, the laser catheter 1010 is able totranslate proximally while the sheath 1120 remains stationary within thevascular occlusion. Upon introducing the liquid medium into the sheath1120 in front of the laser catheter 1010, the laser may be activated,thereby creating laser-induced pressure waves in the presence of theliquid medium. At least a portion of the laser-induced pressure wavesare directed radially, and as the laser catheter 1010 translatesproximally within the sheath 1120, the laser-induced pressure wavestransmit through the sheath 1120 and/or the sheath 1120 itself expandsand contracts, thereby disrupting the remainder of the vascularocclusion 1150′″.

To ensure that the majority of the remainder of the vascular occlusion1150′″ is disrupted, and if desired, disrupt the intraluminal layerand/or the tissues of the blood vessel and the vascular occlusion, thelaser catheter 1010 may be repeatedly translated distally and proximallywithin the sheath 1120. As discussed above, disruption of theintraluminal layer and/or tissues of the blood vessel and the vascularocclusion, can improve the vasculature's ability to absorb drugs,particularly when such drugs are applied with a drug eluting balloon.Also, it is contemplated that prior to, during and/or after any step inthe process outlined in FIG. 19, the laser catheter 1010 may be usedindividually to ablate a portion of the vascular occlusion, or the lasercatheter 1010 may be used in conjunction with the sheath 1120.

As discussed above, transmitting pulses of light energy from an emitterinto a liquid medium creates laser-induced pressure waves and/or vaporbubbles and cavitation events resulting in additional pressure wavesthat disrupt at least a portion of a vascular occlusion. The cathetermay include a guidewire lumen through which a guidewire can pass andcross the vascular occlusion. It may also be desirable to excite andvibrate the guidewire to increase the guidewire's ability to pierce andcross the vascular occlusion. Accordingly, the present disclosure alsocontemplates directing the laser light energy emitted by the emitterinto the liquid medium in a direction which causes the liquid medium topropagate pressure waves toward the guidewire lumen and/or guidewiresuch that the pressure waves excite and vibrate the guidewire.

Referring to FIG. 20, there is depicted a cross-sectional view of thedistal end of system 1610 including a laser catheter 1612 radiallydisposed within a sheath 1614. As shown, the distal end of the catheter1612 includes one or more layers of optical fibers 1616 arrangedcircumferentially around an inner guidewire lumen 1618 that receives aguidewire 1620. The inner layer of optical fibers 1616 extends to thedistal tip 1626 of the catheter 1612 and terminates at the distalemitter 1622 within the catheter 1612. The liquid medium may beintroduced distal to the catheter 1612 through a lumen in the catheter1612 (for example, the guidewire lumen 1618), a lumen in the sheath 1614(not shown), and/or the lumen or space between the laser catheter 1612and the sheath 1614.

Continuing to refer to FIG. 20, in addition to having a plurality ofoptical fibers 1616 and a guidewire lumen 1618, the catheter 1612 mayalso include an outer band 1624 that surrounds the distal tip 1626,thereby increasing the strength and rigidity of the distal tip 1626. Asmentioned above, the present disclosure contemplates directing the laserlight energy emitted by the emitter 1622 into the liquid medium in adirection which causes the liquid medium to propagate pressure wavestoward the guidewire lumen 1618 and/or the guidewire 1620 such that thepressure waves excite and vibrate the guidewire 1620. A means fordirecting laser light emitted from the emitter 1622 towards theguidewire lumen 1618 or the guidewire 1620 includes disposing theemitter 1622 proximate the distal tip 1626 of the catheter 1612 and/orproximate the distal end of the outer band 1624 such that the emitter1622 is recessed from the distal tip 1626 of the catheter 1612 and/orproximate the distal end of the outer band 1624 along the longitudinalaxis of the catheter 1612. By recessing the emitter 1622 from the distaltip 1626 of the catheter 1612 and/or proximate the distal end of theouter band 1624, the pressure waves may be directed toward the guidewirelumen 1618 and/or the guidewire 1620.

An additional means for directing laser light emitted from the emitter1622 towards the guidewire lumen 1618 and/or the guidewire 1620 includesdirecting the emitter 1622 toward the guidewire lumen 1618 or theguidewire 1620. For example, as discussed above, the term “emitter” asused herein may refer to an end portion of a fiber or an opticalcomponent that emits light from a distal end thereof. The emitter 1622is directed towards the guidewire lumen 1618 and/or the guidewire 1620because the optical fiber is tapered in a manner that the light emittedtherefrom is directed radially inward towards the guidewire lumen 1618and/or the guidewire 1620. As illustrated in FIG. 20, the guidewirelumen 1618 and/or guidewire 1620 may extend longitudinally distal of theemitter 1622. Accordingly, as the laser light is emitted from theemitter 1622, the light interacts with the liquid medium, and the liquidmedium absorbs the light energy, thereby creating laser-induced pressurewaves and/or vapor bubbles and additional resultant pressure waves thatcause the guidewire lumen 1618 and/or guidewire 1620 to excite and/orvibrate.

Referring to FIG. 20′, there is depicted an alternate embodiment of thepresent disclosure, particularly an alternate embodiment of a means fordirecting laser light emitted from the emitter 1622 towards theguidewire lumen 1618 and/or the guidewire 1620. Similar to theembodiment discussed above with respect to FIG. 20, the system 1610′ inFIG. 20′ includes a catheter 1612′ having a plurality of optical fibers1616, a guidewire lumen 1618, and an outer band 1624 that surrounds thedistal tip 1626. This embodiment also includes a cap 1628 having aguidewire lumen 1630 extending therethrough.

The cap 1628 can be either removably coupled to the catheter 1612′,particularly removably coupled to the outer band 1624, or the cap 1628can be permanently affixed to the catheter 1612′, particularlypermanently affixed to the outer band 1624. The cap 1628 includes aproximal (for example, interior) side 1632 and a distal (for example,exterior) side 1634. The interior side 1632 is tapered such that acavity 1636 forms between the distal end of the catheter 1612′ and theinterior side 1632 of the cap 1628, thereby allowing the liquid mediumto enter and collect within the cavity 1636. Although FIG. 20′ isdepicted as having a catheter 1612′ with a flush distal end and atapered, recessed cap 1628 to create the cavity 1636 between thecatheter 1612′ and the cap 1628 for the liquid medium to collect, thepresent disclosure also contemplates having a catheter with a recesseddistal end, as depicted in FIG. 20, that could be used in conjunctionwith a cap 1628 having a flush or recessed interior side 1632 to createa cavity for the liquid medium to collect. Accordingly, as the laserlight is emitted from the emitter 1622, the light interacts with theliquid medium within the cavity, and the liquid medium absorbs the lightenergy, thereby creating laser-induced pressure waves and/or vaporbubbles and additional resultant pressure waves that cause the guidewirelumen 1618 and/or guidewire 1620 to excite and/or vibrate.

The sheath 1614 may be, for example, any of the sheaths describedherein. In some embodiments, the sheath 1614 may be the sheath 1140shown in FIGS. 11A-11D, and the catheter 1612 or 1612′ may betranslatably carried therein. Referring now to FIGS. 20″ and 20′″,systems 1610″ and 1610′″ include laser catheters 1612 and 1612′,respectively. The systems 1610″ and 1610′″ also include a sheath 1614′that translatably carries the catheters 1612 and 1612′, respectively.The sheath 1614′ may be the sheath 1120″ shown in FIGS. 18-18E. That is,the sheath 1614′ includes a sleeve or jacket 1122″ and an attenuatingmember 1124″, which may be any of the attenuating members describedherein.

The attenuating member 1124″ has multiple purposes, as follows: (1)reinforcing the sleeve 1122″ and/or the sheath 1614′; (2) reducing orpreventing the formation of vapor bubbles exterior of the attenuatingmember 1124″, the sleeve 1122″ and/or the sheath 1614′; (3) redirectingat least a portion of the pressure waves toward the guidewire lumen 1618and/or guidewire 1620 to excite and/or vibrate the guidewire 1620.Accordingly, the attenuating member 1124″ acts as (1) a means forreinforcing the sleeve 1122″ and/or the sheath 1614′; (2) a means forreducing or preventing the formation of vapor bubbles exterior of theattenuating member 1124″, the sleeve 1122″ and/or the sheath 1614′; (3)a means for redirecting at least a portion of the pressure waves towardthe guidewire lumen 1618 and/or guidewire 1620 to excite and/or vibratethe guidewire 1620.

Further details regarding the first and second purposes of theattenuating member 1124″ are described in connection with FIG. 18.Regarding the ability of the attenuating member 1124″ to redirect atleast a portion of the pressure waves toward the guidewire lumen 1618and/or guidewire 1620 to excite and/or vibrate the guidewire 1620, thepressure waves or portion of the pressure wave(s) that do not passthrough the attenuating member 1124″ may be redirected by theattenuating member 1124″ toward the guidewire lumen 1618 and/orguidewire 1620 to excite and/or vibrate the guidewire 1620. The sizes ofthe openings 1126″ of the attenuating member 1124″ (see FIG. 18) may beselected to control the amplitude or direction of the pressure wavesthat are reflected toward the guidewire lumen 1618, guidewire 1620and/or targeted tissue.

Also, similar to the discussion included above with respect to FIG. 18the attenuating member 1124″ depicted in FIGS. 20″ and 20′″ is shown atthe distal end of the sheath 1614′. The attenuating member 1124″,however, may alternatively and/or additionally as be disposed at theproximal end of the sheath 1614′, the central portion of the sheath1614′, any location or multiple locations between the proximal end anddistal end of the sheath 1614′, or in the entire length or substantiallythe entire length of the sheath 1614′. Therefore, as the catheter 1612or 1612′ translates within the sheath 1614′, the guidewire 1620 willcontinue to excite and/or vibrate.

As described above, for example, with reference to FIG. 13, cathetersystems according to embodiments of the present disclosure may havedistal tips that are fully or partially closed. In some of theseembodiments, it may be desirable to seal the sheath with the guidewireupon introduction of the liquid medium to the closed distal tip. FIGS.21-22B illustrate a catheter system 1710 according to such anembodiment. That is, the catheter system 1710 includes a sheath 1720(which is hidden in FIG. 21 to illustrate internal components of thecatheter system 1710) that has a partially-closed tip 1722. The sheath1720 carries a laser catheter, such as the laser catheter 1010 describedherein, and the laser catheter 1010 may translate distally and/orproximally within the sheath 1720. As shown in FIG. 21, the sheath 1720may taper proceeding distally toward the tip 1722. Alternatively, thesheath 1720 may include a flat surface that receives the tip 1722. Asanother alternative, the tip 1722 may have a similar size to the lumenof the sheath 1720 and be press-fittingly received in the lumen. Inorder to ensure that a cavity remains between the distal end of thelaser catheter 1010 and the proximal end 1724 of the tip 1722 of thesheath 1720, the sheath 1720 may include one or more internal stops1726. The shape of the tip 1722 may be configured similar to the tips180 illustrated and described with respect to FIGS. 2-6 such that thecatheter system 1710, including the laser catheter tip 1722, isconfigured such that the energy produced by the pressure waves iscaptured within the cavity and the forces generated by the pressurewaves propagate longitudinally, including in a forward (that is,parallel with the vessel) direction, thereby increasing the tip'sability to disrupt, destroy and/or penetrate the vascular occlusion.

The tip 1722 includes the proximal end 1724, a distal end 1728, and alumen 1730 extending therethrough from its proximal end 1724 to itsdistal end 1728. The tip 1722 also includes a valve that seals theintersection of the tip 1722 and the guidewire 1040 as the guidewire1040 passes through the guidewire lumen 1730. One example of a valve isthat which is depicted in FIGS. 22-22B which illustrate a flange 1732that is disposed at and/or toward the proximal end 1724 of the tip 1722.

Referring back to FIGS. 21-22B, upon introducing the guidewire 1040through the lumen 1730 of the laser catheter 1010 and into the guidewirelumen 1730 of the tip 1722, the guidewire 1040 and tip 1722 are slidablycoupled such that the tip 1722 can slide over the guidewire 1040 (or theguidewire 1040 can slide through a lumen 1730 of the tip 1722), asdepicted in FIG. 22A. As illustrated in this figure, there is a gap (oropening) caused by the guidewire lumen 1730 between the flange 1732 andthe guidewire 1040. If the gap is maintained during introduction of theliquid medium into the distal end of the catheter system 1710 (via, forexample, the opening or gap between the laser catheter 1010 and thesheath 1720), the liquid medium would travel through the guidewire lumen1730 and into the patient's vasculature, which may be undesirable. Theflange 1732, which may include a tapered portion 1734 that tapers fromthe tip's distal end 1728 toward its proximal end 1724, is configured toradially collapse upon introduction of the liquid medium into the distalend of the catheter system 1710 due to the increased fluid pressure onthe flange 1732. The increased fluid pressure on the flange 1732actuates the flange 1732 and moves it radially inward toward theguidewire lumen 1730 such that the gap between flange 1732 and theguidewire 1040 closes, thereby creating a seal between the betweenflange 1732 and the guidewire 1040, as depicted in FIG. 22B. The reducedthickness of the tapered portion 1734 of the flange 1732 as the flange1732 tapers radially inward towards the guidewire lumen 1730 as theflange 1732 progresses from the distal end 1728 toward the proximal end1724 increases the flange's ability to flex upon exposure to thepressure created upon introduction of the liquid medium. Upon removal ofthe liquid medium from the distal end of the catheter system 1710, thepressure within the catheter system 1710, the pressure on the flange1732 decreases, and the flange 1732 naturally retracts to its originalposition as depicted in FIG. 22A, thereby reestablishing the gap betweenthe tip 1722 and the guidewire 1040 so that the two components may slidewith respect to one another. Accordingly, the flange 1732 acts assealable valve within the tip 1722, and the flange 1732 is actuated withthe introduction and removal of the liquid medium into and from thedistal end of the catheter system 1710.

Although the tapered portion 1734 illustrated in FIGS. 22A and 22Btapers from the tip's distal end 1728 toward its proximal end 1724, thedirection of the taper may be reversed such that the tapered portion1734 tapers from the tip's proximal end 1724 toward its distal end 1728.Additionally, the flange 1732 may taper towards any portion along itslength such that a portion of the flange 1732 is thinner at one or morelocations along its length in comparison to other locations along itslength. Accordingly, upon an increased fluid pressure being imparted onthe flange 1732, thinner portion of the flange 1732 actuates and movesradially inward toward the guidewire lumen 1730 such that the gapbetween flange 1732 and the guidewire 1040 closes, thereby creating aseal between the between flange 1732 and the guidewire 1040.

The tip 1722 may be constructed from any type of compressible orcompliant biopolymers, such as silicones or flouro-polymers, compliantadhesives, etc. The configuration of the tip 1722 depicted in thesefigures includes an exterior wall 1736 and the flange 1732 disposedradially therein, to create a gap therebetween for the liquid medium toenter and actuate the flange 1732. The flange 1732 is also depicted asbeing disposed toward the proximal end 1724 of the tip 1722, whichitself is depicted as tubular, and its distal end 1728 has an inwardtaper that tapers distally from the exterior wall 1736 towards theguidewire lumen 1730. Although the tip 1722 is depicted as includingparticular components and shapes, the present disclosure shall includeother shapes and components known to one of skill in the art. Moreover,the tip 1722 may alternatively include a self-sealing tube constructedof any type of compressible or compliant biopolymers, such as siliconesor flouro-polymers, compliant adhesives, etc. For example, the tip 1722may include a tube that has a lumen 1730 passing therethrough such thatupon insertion of a guidewire, the lumen expands, and upon removable ofthe guidewire, the lumen contracts, thereby appearing as a slit.

Continuing to refer to FIGS. 21-22B, the tip 1722 may include one ormore openings 1738 through its exterior wall 1736. The openings 1738allow the liquid medium to reach the flange 1732 not only from the gapbetween the flange 1732 and the exterior wall 1736 at the proximal end1724 of the tip 1722 but also at a location distal the proximal end 1724of the tip 1722. Allowing the liquid medium to reach the flange 1732 ator toward its distal portion, potentially increases the likelihood andeffectiveness of actuating the flange 1732. Although the tip 1722 isillustrated as having a tubular section 1740 from its proximal end 1724and a tapered section 1742 from the end of its tubular section 1740toward the tip's distal end 1728, the scope of this disclosure shallinclude other shapes for the tip 1722.

As discussed herein, as the laser light is emitted from the emitter(s),the light interacts with the liquid medium, and the liquid mediumabsorbs the light energy, thereby creating vapor bubbles within thecatheter system 1710. The openings 1738 within the tip 1722 may reducethe size of the bubble formed within the catheter system 1710 and/orreduce the likelihood that the bubble will expand toward the distal endof the catheter system 1710.

In some embodiments, the devices and methods of the present disclosurecan also be used deliver laser-induced pressure waves to ablate avascular occlusion using a substantially solid light absorbing materialinstead of liquid medium. In some circumstances, pairing a laser thatemits a specific wavelength of light with a light absorbing materialdesigned to absorb light at that wavelength can significantly increasethe energy efficiency of the resultant laser-induced pressure wavesproduced by the reaction. The use of such pairings can ultimately reducethe energy input required to treat a vascular occlusion, which canincrease the safety of the procedure and reduce costs. For example, thecatheters according to embodiments of the present disclosure can befilled with air or a substantially inert liquid medium (for example,saline) instead of contrast medium, which can significantly reduce theamount and size of vapor bubbles produced along with the laser-inducedpressure waves. Because the laser-induced pressure waves can propagateoutside of the catheter to ablate a vascular occlusion, it can beadvantageous in some circumstances to reduce (for example, by fillingthe catheter with saline) or eliminate (for example, by filling thecatheter with air or inert gas) the production of vapor bubbles. Inother cases, liquid medium delivered to the distal end of the cathetercan be pre-treated to remove the amount of gas dissolved in it usingmethods known to one of ordinary skill in the art based on the presentdisclosure, as this can also reduce the amount of vapor bubblesgenerated along with the laser-induced pressure waves.

Suitable light absorbing material can be any agent capable of absorbinglight energy and producing a laser-induced pressure wave. For example,the light absorbing material can contain an aromatic hydrocarbon withiodine bonded to it, such as iodinated x-ray contrasts. Low osmolar,non-ionic, iodinated, and radio-opaque contrasts are also suitable lightabsorbing materials that can be used to produce laser-induced pressurewaves. Other light absorbing materials include, but are not limited to,iodinated contrasts such as Diatrizoic acid, Metrizoic acid, lodamide,lotalamic acid, loxitalamic acid, loglicic acid, Acetrizoic acid,locarmic acid, Methiodal, Diodone, Metrizamide, lohexol, loxaglic acid,lopamidol, lopromide, lotrolan, loversol, lopentol, lodixanol, lomeprol,lobitridol, loxilan, lodoxamic acid, lotroxic acid, loglycamic acid,Adipiodone, lobenzamic acid, lopanoic acid, locetamic acid, Sodiumiopodate, Tyropanoic acid, Calcium iopodate, lopydol, Propyliodone,lofendylate, Lipiodol, non-iodinated contrasts such as Barium sulfate,MRI contrast agents such as Gadobenic acid, Gadobutrol, Gadodiamide,Gadofosveset, Gadolinium, Gadopentetic acid, Gadoteric acid,Gadoteridol, Gadoversetamide, Gadoxetic acid, Ferric ammonium citrate,Mangafodipir, Ferumoxsil, and Ferristene Iron oxide nanoparticles,Perflubron, Glucose and other carbohydrates, Albumen and other proteins,Nitroglycerin or other vasodilators, Hydrocarbons such as Oils,Alcohols, or other organic functional groups (Amines, Alkanes, Carboxyl,and the like), blood/tissue products such as Platelet Rich Plasma (PRP),packed red cells, plasma, platelet, fat, Charcoal, biocompatiblematerials such as stainless steel, biopolymers, and bioceramics, orother pharmacological agents which contain a combination of aromaticcarbon rings and functional groups such as Salicylic acid,Acetylsalicylic acid, Methyl salicylate, Mesalazine, Aspirin,Acetaminophen, Ibuprofen, Clopidogrel, or other pharmacological and/orbiological agents which may be compatible with the medical proceduresdescribed herein.

Suitable light absorbing material can also include those materialscapable of absorbing wavelengths in the UV spectrum. For example, lightabsorbing materials can include, but are not limited to, PABA, Padimate0, Phenylbenzimidazole sulfonic acid, Cinoxate, Dioxybenzone,Oxybenzone, Homosalate, Menthyl anthranilate, Octocrylene, Octylmethoxycinnamate, Octyl salicylate, Sulisobenzone, Trolamine salicylate,Avobenzone, Ecamsule, 4-Methylbenzylidene camphor, Tinosorb M, TinosorbS, Tinosorb A2B, Neo Heliopan AP, Mexoryl XL, Benzophenone-9, Uvinul T150, Uvinul A Plus, Uvasorb HEB, Parsol SLX, or Amiloxate, Silicon andits various atomic structures, Cadmium telluride, Copper indium galliumselenide, Gallium arsenide, Ruthenium metalorganic dye, Polyphenylenevinylene, Copper phthaloncyanine, Carbon fullerenes and derivatives,Carbon compounds such as Graphite, Graphene, Diamond, Charcoal, Titaniumand oxides, Nickel and oxides, Gold, Silver, Zinc and oxides, Tin andoxides, Aluminum and oxides, or alloys or ceramics of the precedingmetals.

Light absorbing material may be combined with various other compounds tofacilitate their attachment to a substrate. For example, light absorbingmaterials may be combined with various compounds (for example,solubilizing agents) that aid in the generation of a solution or mixturecomprising the light absorbing material, which can be used to coat thesubstrate. In some embodiments, a biodegradable and biocompatiblehydrophobic polymer may be used as a light absorbing material. Forexample, the biodegradable and biocompatible hydrophobic polymer may bepoly(glycerol sebacate acrylate) (PGSA), or variations and combinationsthereof, which can be crosslinked using ultraviolet light. Ultravioletlight may be emitted from the distal end of a catheter, which may bedisposed within or outside of a sheath, to activate the PGSA, forexample.

Other light absorbing material can also include agents havingadhesive-like properties, and in some cases, the light absorbingproperties of these agents can be in addition to, or independent of,their use as adhesives. For example, light absorbing materials caninclude, but are not limited to, cyanoacrylates, bovine serum albumin(BSA)-glutaraldehyde, fibrin sealants, gelatin matrix thrombin, gelatinsponge, oxidized cellulose, collagen sponge, collagen fleece,recombinant factor VIIa, and the like. In some embodiments, the lightabsorbing material may comprise hydrophobic functional groups, such ashexanoyl (Hx; C6), palmitoyl (Pam; C16), stearoyl (Ste; C18), and oleoyl(Ole; C18 unsaturated) groups, so as to resist being washed out ordisengaged from their substrate in predominately aqueous environments(for example, vascular tissue). Such light absorbing materials caninclude, but are not limited to, 10Ole-disuccinimidyl tartrate,10Ste-disuccinimidyl, and variations and combinations thereof.

Light absorbing material can be configured to exhibit high absorption oflight energy from an emitter. Light energy can be emitted at anysuitable wavelength capable of generating laser-induced pressure waves.Light energy can be emitted between about 1 nanometer and about 1millimeter. In some cases, light can be emitted from about 10 nanometersto about 5000 nanometers. In some cases, light can be emitted from about100 nanometers to about 1000 nanometers. In some cases, light can beemitted from about 250 nanometers to about 750 nanometers. In somecases, light can be emitted from about 300 nanometers to about 600nanometers. In still other cases, light can be emitted from about 300nanometers to about 350 nanometers.

In general, the light absorbing material can be located anywhere withina catheter, so long as it generally intersects with the path of lightemitted from the optical fibers. In some embodiments, the lightabsorbing material may be substantially solid (for example, stable in agenerally solid state, such as metals and metal alloys). Substantiallysolid light absorbing material can be used to construct various portionsof the components of the catheter, and/or substantially solid lightabsorbing material can be used to construct a separate structure that isindependent of another catheter component.

In some embodiments, the light absorbing material can be applied to aseparate supporting structure (that is, a support structure that is notpredominately made of light absorbing material, or a support structurethat is not being used as a light absorbing material) and used togenerate laser-induced pressure waves using the devices and methods ofthe present disclosure. In some embodiments, the light absorbingmaterials are stable only in liquid, gel, or semi-liquid forms. In theseembodiments, the light absorbing material can be included as part of aformulation or coating that is suitable for application to a supportstructure, such as impregnated in hydrogel or other solid supportmatrix. In some embodiments, the light absorbing materials can be partof a formulation or coating containing other agents that facilitatetheir placement on and/or adherence to a support structure. For example,solid absorbing materials can be formulated with coating agents,thickening agents, adhesive agents, and/or other pharmaceutical orbiological agents that are suitable for use with the devices and methodsof the present disclosure.

Referring to FIG. 23, the distal end of a catheter system 1810 includinga light absorbing material according to an embodiment of the presentdisclosure is illustrated. The catheter system 1810 is similar to thecatheter system 1710. That is, the catheter system 1810 includes asheath 1820 (which is hidden in FIG. 23 to illustrate internalcomponents of the catheter system 1810) that has a partially-closed tip1822. The sheath 1820 carries a laser catheter, such as the lasercatheter 1010 described herein, and the laser catheter 1010 maytranslate distally and/or proximally within the sheath 1820. As shown inFIG. 23, the sheath 1820 may taper proceeding distally toward the tip1822. Alternatively, the sheath 1820 may include a flat surface thatreceives the tip 1822. As another alternative, the tip 1822 may have asimilar size to the lumen of the sheath 1820 and be press-fittinglyreceived in the lumen. In order to ensure that a cavity remains betweenthe distal end of the laser catheter 1010 and the proximal end of thetip 1822 of the sheath 1820, the sheath 1820 may include one or moreinternal stops 1826. The shape of the tip 1822 may be configured similarto the tips 180 illustrated and described with respect to FIGS. 2-6 suchthat the catheter system 1810, including the laser catheter tip 1822, isconfigured such that the energy produced by the laser-induced pressurewaves is captured within the cavity and the forces generated by thelaser-induced pressure waves propagate longitudinally, including in aforward (that is, parallel with the vessel) direction, therebyincreasing the tip's ability to disrupt, destroy and/or penetrate thevascular occlusion.

The tip 1822 may include the same features and structures as the tip1722. In addition, the tip 1822 includes a light absorbing materialsupport structure 1824. The light absorbing material support structure1824 acts as a substrate for the application of light absorbingmaterial, which may be any of the light absorbing materials describedherein. Light absorbing material can be applied as a coating, asdescribed herein, on the proximal end of the tip 1822 within the cavityof the catheter system 1810, and light absorbing material supportstructure 1824 can be positioned such that it generally intersects withthe path of the light emitted from the distal end of the laser catheter1010.

In some embodiments, the light absorbing material can be applied tovarious surfaces within the catheter system 1810 itself instead of beingapplied to a support structure. For example, the light absorbingmaterial can be applied as a coating to the inner surface of thecatheter system 1810 or portions thereof (such as the inner surface ofthe sheath 1820). The laser light emitted from the distal end of thelaser catheter 1010 can be directed upward and/or outward such that itcan react with the light absorbing material to generate a laser-inducedpressure wave, without the need for an additional support structure.

Referring to FIG. 24, the distal end of a catheter 1910 including alight absorbing material according to an embodiment of the presentdisclosure is illustrated. The catheter 1910 is similar to the catheterillustrated in FIG. 5A. That is, the catheter 1910 includes a distal endhaving a tip 1912 that comprises a non-metallic component in lieu of ametallic (for example, stainless steel) solid or hollow construction.The catheter 1910 includes an outer sheath 1914, an inner sheath 1916disposed concentrically and/or radially within the outer sheath 1914,and one or more optical fibers 1918 disposed concentrically and/orradially within the inner sheath 1916. The distal end of the outersheath 1914 is directly coupled (via a press fit and/or a weld) to thetip 1912. The inner sheath 1916 and the one or more optical fibers 1918are not directly coupled to the tip 1912. Rather, the inner sheath 1916and the one or more optical fibers 1918 are disposed proximate the tip1912, thereby forming a cavity among the outer sheath 1914, the innersheath 1916, one or more optical fibers 1918, and the tip 1912.

The catheter 1910 may include a shield 1920 disposed axially between thedistal end of the inner sheath 1916 and the proximal end of the tip1912, and disposed radially between the one or more optical fibers 1918and the outer sheath 1914. The shield 1920, which is depicted as agenerally cylindrical tube, increases the laser-induced pressure waves'resistance in the radial direction, thereby reducing the ability of thelaser-induced pressure waves to travel radially towards the outer sheath1914. The configuration of the cylindrically-shaped shield 1920 allowsfor a reduced resistance in the longitudinal direction, in comparison tothe radial direction, thereby increasing the tip's ability to translatein a forward/backward direction. The cylindrically-shaped shield 1920may also be configured such that its diameter is greater (or less) atits proximal end in comparison to its distal end, thereby potentiallytapering in either the proximal or distal direction and concentratingthe laser-induced pressure waves towards the center of the tip 1912. Theshield 1920 may also serve to create a sealed cavity at the distal endof the catheter 1910, thereby preventing the leakage of the liquidmedium through the outer sheath 1914 because a portion of the shieldoverlaps with a portion of the outer sheath 1914 that may be porous.

The inner sheath also includes one or more lumens for passage of liquidmedium into the cavity. The distal end(s) of the one or more opticalfibers 1918 are proximate, at, or distal the distal end of the innersheath 1916. Again, one or more emitters are disposed at the distal endof the one or more optical fibers 1918. The emitter(s) are in directcontact with the liquid medium, such that when laser light energy isemitted from the emitter(s), the liquid medium absorbs the emittedlight, which in turn produces laser-induced pressure waves and generatesvapor bubbles and/or cavitation events that produce additional pressurewaves.

The tip 1912 has a circular construction, thereby creating a collar forthe distal end of the outer sheath 1914. The tip 1912 also includes aflexible membrane 1922 at its distal end. For example, the membrane 1922may be constructed of Mylar and be adhesively bonded to the distal endof the tip 1912 in an orientation perpendicular to the longitudinalaxis. In addition the membrane may be compliant in order to deflect andengage the shape of the calcified cap, total occlusion or lesion. Insome embodiments, the membrane 1922 may be constructed of an elastic orhyperelastic material (for example, nitinol).

The membrane 1922 carries a light absorbing material support structure1924 within the cavity. The light absorbing material support structure1924 acts as a substrate for the application of light absorbingmaterial, which may be any of the light absorbing materials describedherein. In other embodiments, the light absorbing material supportstructure 1924 could be carried by the membrane 1922 outside of thecavity, or light absorbing material can be applied as a coating, asdescribed herein, on the membrane 1922 (with the cavity or outside ofthe cavity). In any case, the light absorbing material can be positionedsuch that it generally intersects with the path of the light emittedfrom the distal end of the optical fiber(s) 1918. In some embodimentsand as shown in FIG. 24, the light absorbing material support structure1924 may cover the entire membrane 1922 within the cavity. In otherembodiments, the light absorbing material support structure 1924 maypartially cover the membrane 1922 within the cavity. In theseembodiments, the position and/or size of the light absorbing materialsupport structure 1924 on the membrane 1922 may affect the location ofvapor bubble formation and collapse, which in turn may affect thedeflected shape of the membrane 1922. In some embodiments, the lightabsorbing material can be applied to various surfaces other within thecatheter 1910 instead of being applied to a support structure. Forexample, the light absorbing material can be applied as a coating to theinner surface of the shield 1920 or portions thereof.

To treat a subject having a vascular occlusion, the distal end of thecatheter 1910, particularly the tip 1912 is positioned adjacent to thevascular occlusion with the membrane 1922 adjacent the vascularocclusion. The liquid medium may be delivered to the cavity from the onemore lumens within the inner sheath 1916 through one or more liquidmedium ports or between the outer sheath and the inner sheath or lasercatheter 1910. When the laser system is activated, light energy travelsthrough one or more optical fibers until the light energy is releasedfrom the emitter(s) at the end of the one or more optical fibers. As thelight absorbing material and the liquid medium absorb the light energy,a laser-induced pressure wave forms, the liquid medium rapidly displacesoutward and inward, creating a vapor bubble. The energy produced by thelaser-induced pressure wave and vapor bubble is captured within theclosed system provided by the cavity and transferred to the vascularocclusion through the flexible membrane 1922. The transfer of the energyproduced by the laser-induced pressure waves to the vascular occlusionis sufficient to disrupt calcium deposits and/or fibrous tissue withinthe vascular occlusion. The forces generated by the laser inducedpressure waves can propagate longitudinally in forward (that is,parallel to the vessel). Pressure waves produced in this manner can alsobe used to increase vessel compliance prior to performing anotherprocedure, such as a traditional balloon angioplasty.

As discussed above with respect to FIGS. 12 and 19, the presentdisclosure discusses using a laser catheter to ablate 1010 at least aportion of the vascular occlusion or restriction in the vessel of thesubject prior to using the combination of the laser catheter 1010(depicted in FIG. 10) and a sheath 1120 (depicted in FIG. 18) to createlaser-induced pressure waves in the presence of a liquid medium anddisrupt a portion of the vascular occlusion. FIGS. 25-26F are includedto illustrate the formation of a vascular occlusion within thevasculature of a subject that is treated with the laser catheter 1010and the sheath 1120. Referring to FIG. 25, there is depicted across-sectional view of a healthy arterial wall 2000 taken along adirection perpendicular to the longitudinal axis of the arterial wall. Ahealthy arterial wall 2000, or vascular wall, typically includes anouter layer referred to as the “adventitia” or “adventicia” which isshown in FIG. 25 as layer 2020. There may be additional layers, such aslayer 2010 of the arterial wall 2000, on the outside of the adventitia.A healthy arterial wall 2000 also includes a middle or central layerreferred to as the media 2030. The media 2030 is located radially inwardof and adjacent to the inner portion of the adventitia 2020. The media2030 has a layers of smooth muscle cells and layers of elastin fiberthat allows the artery to expand and contract. A healthy arterial wall2000 also includes an inner layer referred to as the intima 2040. Theintima 2040 is located radially inward of and adjacent to the media2030. A healthy arterial wall 2000 also includes an endothelium layer2050, which is located on the inner most surface of the intima 2040 andcreates the boundary for the passageway (or inner lumen) 2060.

As mentioned above, the media 2030 is located radially inward of andadjacent to the inner portion of the adventitia 2020. Specifically, anexternal elastic membrane, commonly referred to as the external elasticlamina, 2035 separates the media 2030 from the adventitia 2020. As alsomentioned above, the intima 2040 is located radially inward of andadjacent to the inner portion of the media 2030. An internal elasticmembrane 2025, commonly referred to as the internal elastic lamina,separates the intima 2040 from the media 2030.

Referring to FIG. 25A, there is depicted a smaller version of thestructure of the healthy arterial wall 2000 depicted in FIG. 25. Also,FIG. 26A is a longitudinal-sectional view of the healthy arterial wall2000 taken along a direction parallel to the longitudinal axis of thearterial wall. Specifically, FIG. 26A is a longitudinal-sectional viewof the structure of the healthy arterial wall 2000 taken along line B-Bof FIG. 25A.

Referring to FIG. 26B, over time, fat and/or lipids 2070′ may start tocollect and/or deposit in the intima 2040′ of the arterial wall 2000′ asa result of buildup of fat and lipids in the blood. This disease processis commonly referred to as atherosclerosis and occurs in the arteries ofthe body including the coronary and peripheral arteries. It is thiscollection of fat and/or lipids 2070′ in the intima 2040′ that will leadto the formation of a vascular occlusion that can reduce or completelyobstruct blood flow in the passageway 2060′. Over time this buildup offat and lipids 2070′ becomes a heterogeneous mix 2065″ (commonlyreferred to as plaque) of many constituents including but not limited tofats, lipids, fibrin, fibro-calcific plaque, calcium crystals, thrombus,etc. For example, a portion of the fat and/or lipids 2070′ may turn intoplaque 2065″ and even become calcified, which is depicted as 2055″ inFIG. 26C. As the fat and/or lipids 2070″ collect, turn into plaque 2065″and/or become calcified 2055″, the intima 2040″ starts to inflame andexpand, thereby decreasing the cross-sectional area of the passageway2060″.

Referring to FIG. 26D, as atherosclerotic disease progresses, and thecondition of the arterial wall 2000′″ is left untreated, the plaque2065′″ continue to collect, and the intima 2040′″ continues to expandand decrease the cross-sectional area of the passageway 2060′″. However,upon the intima 2040′{hacek over ( )} of the arterial wall 2000′{hacekover ( )} reaching its limit to expand further, the intima 2040′{hacekover ( )} and the endothelium can rupture 2058′{hacek over ( )} andrelease the plaque contents previously contained in the thickened lipidsand enlarged intima white blood cells into the passageway 2060′{hacekover ( )}, as depicted in FIG. 26E. Platelets and fibrin collect withinthe passageway 2060{hacek over ( )} of the arterial wall 2000{hacek over( )} to try and repair the rupture, and in doing so form a vascularocclusion 2080{hacek over ( )}, which may have calcified portions2085{hacek over ( )}, as depicted in FIG. 26F. This figure alsoillustrates that formation of the vascular occlusion 2080{hacek over( )} further decreases the size of the passageway 2060{hacek over ( )}and in some instances fully obstructs flow.

Referring to FIG. 26D and FIGS. 26G and 26H, a laser catheter 1010 maybe used to debulk or remove plaque buildup contained behind the intima2065′″ or within the vascular occlusion 2080{hacek over ( )}′ or aportion thereof from the passageway of the arterial wall 2000{hacek over( )}′. After debulking the plaque buildup or the occlusive disease, thecombination of the laser catheter 1010 and the sheath 1120 of thepresent disclosure may be used to treat the remaining portion of theplaque buildup 2065′″ or the vascular occlusion 2080{hacek over ( )}′,particularly by disrupting the calcified portions 2085{hacek over ( )}″as depicted in FIG. 26H and/or FIG. 26H′ by creating laser-inducedpressure waves as described previously, to treat the condition of thearterial wall 2000{hacek over ( )}″ as depicted in FIG. 26I.

FIG. 26I illustrates the arterial wall 2000{hacek over ( )}″ with anenlarged passageway 2060{hacek over ( )}″, the majority of the plaque2065′″ or vascular occlusion 2080{hacek over ( )}″ removed, and thecalcification of the remaining portion of the vascular occlusion, alongwith the calcification of the intima 2040{hacek over ( )}″, fractured ormodified making it more amenable to dilation at lower atmosphericpressures. FIGS. 25, 25A and 26A-21I use similar numeric values, but thedifferent figures include different indicators, such as ′ and {hacekover ( )} and combinations thereof, for the numeric values due to thechanges occurring within the arterial wall as the vascular occlusion isformed and treated, which is progressively illustrated from one figureto the next. For purposes of brevity, certain layers of the arterialwall 2000 are omitted from the discussion of particular figures, andnumeric values of certain items of the arterial wall 2000 are omittedfrom the particular figures. Nevertheless, one should consider thelayers of the arterial wall 2000, and the formations therein, to havethe same numeric values even if omitted from FIGS. 25, 25A and 26A-26I.

Referring to FIGS. 27A and 27B, there is a method 2700 of removingplaque buildup or occlusive disease by performing an atherectomyprocedure and treating the remainder of the vascular occlusion withinthe intima using a laser catheter 1010 (depicted in FIG. 10) inconjunction with the sheath 1120 (depicted in FIG. 18) to createlaser-induced pressure waves in the presence of a liquid medium anddisrupt a portion of the vascular occlusion. This method 2700 may beused to treat coronary arteries and/or peripheral arteries including butnot limited to arteries of the vasculature of the legs, the renalarteries, subclavian arteries, etc.

The method 2700 in FIGS. 27A and 27B includes locating a vascularocclusion in the vessel of a subject at step 2705. The next step 2710,which is optional, includes locating a guidewire at the vascularocclusion and/or inserting a guidewire through the vascular occlusion orthrough the passageway past the vascular occlusion. Step 2715 includesperforming an atherectomy procedure to remove the plaque or vascularocclusion or a portion thereof. One type of atherectomy device is anablation catheter, such as a laser ablation catheter 1010 discussedherein, which is capable of ablating at least a portion of the vascularocclusion as depicted in FIG. 26G. Other types of ablation cathetersinclude radiofrequency ablation catheters, microwave ablation catheters,and cryoablation catheters. Atherectomy devices other than ablationcatheters, such as mechanical atherectomy devices, may also be used toremove the vascular occlusion.

After the vascular occlusion (or a portion thereof) is removed from thevasculature, step 2720 may then be performed. Step 2720 includespositioning a sheath 1120 of the present disclosure over a lasercatheter 1010 within vasculature of a subject, as depicted in FIG. 26H,followed by step 2725, which includes positioning the sheath 1120 andlaser catheter 1010 adjacent the vascular occlusion, as depicted in FIG.26H′. For example, if a clinician uses a catheter 1010, which has aguidewire lumen, and a sheath 1120, the catheter 1010 may be slid overthe guidewire 1130 and into the vasculature, and the sheath 1120 issubsequently slid over the catheter 1010, which is then coupled to thesheath 1120. Step 2725 also includes is positioning the sheath 1120 andlaser catheter 1010 adjacent to the vascular occlusion (or remainderthereof). The axial locations of the laser catheter 1010 and the sheath1120 may be adjusted by translating either or both components withrespect to one another. Particularly, the sheath 1120 may be translatedfrom the position depicted in FIG. 26H, which illustrates the lasercatheter 1010 extending beyond the distal end of the sheath 1120, to theaxial locations of the laser catheter 1010 and the sheath 1120 depictedin FIG. 26H′, wherein the emitters of the laser catheter 1010 are withinthe attenuating member of the sheath 1120 and axially aligned with boththe attenuating member and the remainder of the vascular occlusion, andthe corresponding portions of the sheath and attenuating member areadjacent the vascular occlusion (or remainder thereof).

Once the sheath 1120 and laser catheter 1010 are disposed adjacent thevascular occlusion, such that the emitters and the attenuating memberare axially aligned adjacent the vascular occlusion as depicted in FIG.26H′, the liquid medium may be introduced to the distal end of the lasercatheter as set forth in step 2730 of FIGS. 27A and 27B. Continuing torefer to FIGS. 27A and 27B, step 2735 includes activating an energysource, such as a laser, to create laser-induced pressure waves in thepresence of the liquid medium and disrupting a portion of the vascularocclusion. The laser catheter 1010 and sheath 1120 may be used totraverse the entire vascular occlusion or only disrupt a portion of thevascular occlusion. This is, the laser catheter 1010 and sheath 1120 maymove axially with respect to another (between the positions shown inFIG. 26H and FIG. 26H′) and/or together, while emitting laser-inducedpressure waves to disrupt a portion of the vascular occlusion. If thelaser catheter 1010 and sheath 1120 are used to disrupt a portion of thevascular occlusion, then the guidewire 1130 may penetrate and traversethe vascular occlusion as set forth in step 2740.

Activating at least one energy source coupled to at least one emitter ofthe laser catheter, which is surrounded by the sheath 1120, to emit andsend pulses of laser light energy into and/or to react with the liquidmedium to produce propagating laser-induced pressure waves and disrupt aremaining portion of the vascular occlusion. Disrupting the remainingportion of the vascular occlusion, particularly any calcified portionswithin the vascular occlusion, produces cracks in the calcified portionsand/or reduces the size of the calcified portions because thelaser-induced pressure waves disrupt the calcified portions, therebycracking the calcified portions and/or fragmenting the size of thecalcified particles such that the contiguous area is reduced. In somecases, the method 2700 may include an additional step (not shown) ofactivating at least one energy source coupled to at least one emitterenclosed within the sheath to emit and send pulses of laser light energyinto and/or to react with the liquid medium to produce propagatinglaser-induced pressure waves to deliver a therapeutic agent from thesheath to a remaining portion of the vascular occlusion and/or thevascular tissue near the obstruction or restriction.

One of the benefits of the present disclosure is that the catheter 1010and sheath 1120 depicted in FIG. 26H and FIG. 26H′ may optionallyinclude an attenuating member, such as the attenuating member depictedin the sheath 1120 of FIG. 18 above. The attenuating member 1124, or thealternatives illustrated in FIGS. 18A-18F, may reduce or prevent theformation of vapor bubbles on the exterior of the attenuating memberand/or the sheath 1120 and/or reinforces the sheath such as to minimizeor prevent sheath expansion. Reinforcing the sheath and/or reducing orpreventing the formation of vapor bubbles on the exterior of theattenuating member (or sheath) reduces or prevents the outward andinward fluid displacement from dilating the arterial wall whilesimultaneously allowing the laser-induced pressure wave to penetrate thearterial wall and disrupt calcified portions in the vascular occlusionand/or intima. That is, incorporating an attenuating member, reinforcesthe sheath, reduces or preventing the formation of vapor bubbles on theexterior of the attenuating member, potentially inhibits displacement ofthe soft tissue within the arterial wall and possibly reduces orprevents delamination of the layers of the arterial wall.

Referring again to FIGS. 27A and 27B, after performing step 2735 (andpossibly 2740), step 2745 may be performed. Step 2745 includes thecontinued insertion of the liquid medium into the gap between thecombination of the laser catheter 1010 and the sheath 1120, therebycontinuing to disrupt the vascular occlusion with laser-induced pressurewaves, while the laser catheter 1010 remains within the sheath 1120proximal its distal end. Alternatively, the insertion of the liquidmedium may be discontinued and the laser catheter 1010 may be used toablate vascular occlusion as the laser catheter 1010 passes over theguidewire 1130 through the vascular occlusion while the sheath 1120remains proximal of the vascular occlusion as set forth in step 2750.That is, introduction of the liquid medium between the laser catheter1010 and the sheath 1120 may be terminated, and the laser catheter 1010may extend beyond the distal end of the sheath 1120 so that the lasercatheter 1010 can perform additional atherectomy. After the additionalatherectomy procedure is performed, the distal end of the laser catheter1010 may return to a position within the distal end of the sheath 1120,and the liquid medium may again be supplied to the distal end of thelaser catheter 1010 within the sheath 1120, thereby once more creatinglaser-induced pressure waves to disrupt the remainder of the vascularocclusion recently ablated by the laser catheter.

To ensure that the majority of the remainder of the vascular occlusionis disrupted, and if desired, disrupt the intraluminal layer and/ortissues of the blood vessel and the vascular occlusion, the lasercatheter 1010 may be repeatedly translated distally and proximallywithin the sheath 1120, as in step 2745 and/or step 2755. As discussedabove, disruption of the intraluminal layer and/or tissues of the bloodvessel and the vascular occlusion, can improve the vasculature's abilityto absorb drugs, particularly when such drugs are applied with a drugeluting balloon. Also, it is contemplated that prior to, during and/orafter any step in the process outlined in FIG. 19, the laser catheter1010 may be used individually to ablate a portion of the vascularocclusion, or the laser catheter 1010 may be used in conjunction withthe sheath 1120.

As discussed above, transmitting pulses of light energy from an emitterinto a liquid medium creates laser-induced pressure waves and/or vaporbubbles and additional resultant pressure waves that disrupt at least aportion of a vascular occlusion. The catheter may include a guidewirelumen through which a guidewire can pass and cross the vascularocclusion. It may also be desirable to excite and vibrate the guidewireto increase the guidewire's ability to pierce and cross the vascularocclusion. Accordingly, the present disclosure also contemplatesdirecting the laser light energy emitted by the emitter into the liquidmedium in a direction which causes the liquid medium to propagatelaser-induced pressure waves toward the guidewire lumen and/or guidewiresuch that the laser-induced pressure waves excite and vibrate theguidewire.

Although the method illustrated in FIGS. 27A and 27B depicts steps 2705through 2755 of method 2700 as being performed serially, any or all ofthe steps within the method 2700 may in any order and/or in parallelwith any of the other steps. For example, certain steps can be performedwithout performing other steps. Upon completing step 2735 and/or step2740, the combined laser catheter and sheath can optionally berepositioned within the vasculature and adjacent another portionthereof. Similarly, upon completing step 2735 and/or step 2740, theemitter(s) can optionally be repositioned within the sheath. The sheathcan be repositioned within the vasculature and/or the emitter(s) can berepositioned within the sheath. The method 2900 also includes ending theprocedure when the desired therapeutic outcome is obtained, or repeatingany of steps 2905 through 2945 as may be necessary to treat a subjecthaving a vascular occlusion.

Furthermore, a drug eluting (coated) balloon (DEB or DCB) catheter maybe used to deliver drugs to the remnants of the vascular occlusion.Disrupting the remaining portion of the vascular occlusion with thelaser-induced pressure waves prior to utilizing a DEB may increase theeffectiveness of the drugs being applied to the vascular occlusionbecause the laser-induced pressure waves disrupt calcium formed in theintima layer, as well as in tissues within the blood vessel, therebycreating a pathway for the drug to enter the intima and tissues withinthe blood vessel and/or vascular occlusion.

The present disclosure also contemplates using the laser-induced sheathwith conventional angioplasty balloons, as well as with DEBs. Forexample, a surgical procedure may include performing an atherectomy witha laser catheter, using the sheath in combination with the lasercatheter to treat the calcified portions of the vasculature as set forthin FIGS. 27A and 27B above, and then inserting an angioplasty balloon(or DEB) into the vasculature adjacent the relevant portion of thevasculature and expanding the angioplasty balloon to dilate the relevantportion of the vasculature.

As discussed above, the laser-induced pressure waves created by thelaser catheter and sheath of the present disclosure not only disrupt avascular occlusion and/or calcium in the intima layer, the laser-inducedpressure waves created by the catheter of the present disclosure canalso disrupt calcification of the tissues within the vessel wall(s) Thatis, the laser-induced pressure waves may be used to fracture or modifycalcified tissue regardless of whether the vasculature includes anocclusion. For example, patients with medial artery calcification, whichis also known as Minckeberg's sclerosis, could potentially benefit frombeing treated with the catheter of the present disclosure.

Referring to FIG. 28A, there is depicted a healthy arterial wall 2300similar to the arterial wall depicted in FIG. 26A. For example,reference numerals 2010, 2020, 2030, 2040, 2050 and 2060 of FIG. 26Acorrespond to reference numerals 2310, 2320, 2330, 2340, 2350 and 2360of FIG. 28A. That is, reference numerals 2310 and 2320 are the externa,reference numeral 2330 is the media, reference numeral 2340 is theintima, reference numeral 2350 is the endothelium, and reference numeral2360 is the passageway.

Referring to FIG. 28B, there is depicted is a cross-sectional view of anarterial wall 2300′ that includes calcium deposits 2370 formed in themedia 2330. The calcium deposits begin as crystal aggregates andtypically aggregate along the elastin fibrin layers within the media. AsMinckeberg's sclerosis (commonly referred to as medial calcification)progresses, multiple layers of calcium can form that involve up to thefull circumference of the vessel. The calcium can also extend radiallyinto the adventitia and intima layers. Minckeberg's sclerosis (medialcalcification) is caused by a recruitment of calcium by the smoothmuscle cells and is attributed but not limited to common comorbiditiesfound in patients suffering from vascular disease including diabetics,kidney disease patients and other metabolic or hormonal imbalances. Themedia 2330 includes smooth muscle cells and elastin fiber, which allowthe artery to expand and contract. Upon formation of calcium deposits2370, however, the artery's ability to expand and contract is reduced.That is, formation of calcium deposits 2370 in the media 2330 reducesthe compliance of the artery 2300′, which in turn potentially reducesthe amount of blood flow through such arteries and can potentiallynegatively affect other health conditions, such as diabetes. Thiscondition can occur with atherosclerotic disease as described previouslyor be an isolated condition without the narrowing of the lumen of theartery.

The combined catheter 1010 and sheath 1120 of the present disclosure areable to create laser-induced pressure waves, which fracture or disruptthe calcium deposits 2370 in the media 2330 of the arterial wall 2300″as shown in FIG. 28C, thereby increasing the compliance of the arterialwall 2300′″ and blood flow therethrough while minimizing or preventingdilation of the arterial wall. That is, one of the benefits of thepresent disclosure is that the sheath depicted in FIG. 28C, mayoptionally include an attenuating member, such as the attenuating member1124 depicted in FIG. 18 above. The attenuating member 1124, or thealternatives illustrated in FIGS. 18A-18F, may reduce or prevent theformation of vapor bubbles on the exterior of the attenuating memberand/or reinforce the sheath such as to minimize or prevent itsexpansion. Reinforcing the sheath and/or reducing or preventing theformation of vapor bubbles on the exterior of the attenuating memberreduces or prevents outward and inward fluid displacement from expandingand contracting the arterial wall while simultaneously allowing thelaser-induced pressure wave to penetrate the arterial wall and disruptcalcium deposits in the tissue (e.g., media) and/or tissue layers (e.g.,media layer) of the blood vessel.

FIGS. 28A-28D use similar numeric values, but the different figuresinclude different indicators, such as ′ and {hacek over ( )} andcombinations thereof, for the numeric values due to the changesoccurring within the arterial wall as the calcium is formed and treated,which is progressively illustrated from one figure to the next. Forpurposes of brevity, certain layers of the arterial wall 2300 areomitted from the discussion of particular figures, and numeric values ofcertain items of the arterial wall 2300 are omitted from the particularfigures. Nevertheless, one should consider the layers of the arterialwall 2300, and the formations therein, to have the same numeric valueseven if omitted from FIGS. 28A-28D.

Referring to FIG. 29, there is depicted a method 2900 of using acatheter to generate laser-induced pressure waves to treat the calciumdeposits in the tissue (e.g., media) and/or tissue layers (e.g., medialayer) of the blood vessel by disrupting the calcium deposits toincrease vasculature compliance, thereby increasing blood flowtherethrough. This method 2900 may be used to treat calcium deposits inthe tissue(s) of coronary arteries and/or peripheral arteries. Themethod 2900 in FIG. 29 includes locating a calcification of the tissue(e.g., media) and/or tissue layers (e.g., media layer) within thevasculature of a subject at step 2910. The next step 2920, which isoptional, includes positioning a guidewire within the vasculature of asubject.

After locating the calcified portion(s) of the tissue (e.g., media)and/or tissue layers (e.g., media layer) within the vasculature, step2930 may then be performed. Step 2930 includes introducing to thevasculature a laser catheter of the present disclosure and a sheath ofthe present disclosure over the laser catheter. Step 2940 includespositioning within the vasculature the sheath and the laser catheter(and optionally the guidewire) such that an attenuating member withinthe sheath is adjacent the portion of vasculature having thecalcification, and the distal end of the laser catheter is disposedwithin the attenuating member adjacent the vasculature that includes thecalcified portion(s). For example, if a clinician uses a laser catheter1010 described herein, which has a guidewire lumen, the laser cathetermay be slid over the guidewire and into the vasculature such that theemitter(s) of the laser catheter are positioned adjacent to thevasculature that has the calcification. A sheath 1120 of the presentdisclosure is then slid over the laser catheter 1010 to a positionwithin the vasculature such that the attenuating member is adjacent thevasculature that includes the calcified portion(s). Accordingly, theemitter will be disposed within the portion of the sheath comprising theattenuating member.

The method 2900 also includes step 2950, which comprises introducing theliquid medium (for example, contrast medium) having light absorbingmaterial to the distal end of the laser catheter, wherein the lasercatheter is disposed within the sheath, and preferably within theportion of the sheath comprising the attenuating member. At step 2960,the emitters on the laser catheter are activated, thereby initiating theformation of laser-induced pressure waves a portion of which at leastpass through the sheath, including the attenuating member, therebydisrupting the calcium in the vasculature. That is, the laser-inducedpressure waves crack the calcified portion(s) and/or break the calcifiedportions of the tissue (e.g., media) and/or tissue layers (e.g., medialayer) into smaller particles. Disrupting the calcified portion(s)within the tissue(s) of the blood vessel cracks the calcified portion(s)because the laser-induced pressure waves are absorbed by the calcifiedportions, thereby increasing the arterial wall's compliance, which inturn leads to improved blood flow and positive implications for otherhealth conditions.

Step 2970 of method 2900 may include continuing to insert liquid mediumto the distal end of the laser catheter and axially translate the lasercatheter and/or the sheath to disrupt a portion of the calcified tissuesof the blood vessel in the same portion or other portions of thevasculature. And any of the steps of method 2900 may be repeated until asufficient amount of calcium is disrupted and the arterial wall'scompliance is satisfactorily increased, as set forth in step 2980.

Additionally, although it is not disclosed in FIG. 29, in some cases,the method 2900 may include the step of activating at least one energysource coupled to at least one emitter enclosed within the sheath toemit and send pulses of laser light energy into and/or to react with theliquid medium to produce propagating laser-induced pressure waves todeliver a therapeutic agent from the exterior of the sheath to throughthe cracks in the calcified portions through the cracks in the calcifiedportions and/or through (or to) potentially.

Referring to FIG. 30, there is depicted a kit 3000 that includes a lasercatheter assembly 3008 and a sheath assembly 3004. Sheath assembly 3004may also be referred to as outer sheath assembly 3004 due to itsdisposition with respect to the laser catheter assembly 3008. FIG. 31depicts the sheath assembly 3004 shown in FIG. 30, and FIG. 32 depictsthe laser catheter assembly 3008 shown in FIG. 30. The sheath assembly3004 may include a proximal end portion, a distal end portion 3040 and asheath 3012 having a working length of about between 50 cm and 200 cm,including 140 cm, and a lumen 3024 extending between such ends. Thesheath 3012 may also be referred to as the outer sheath 3012 due to itsdisposition with respect to the laser catheter assembly 3008. The distalend portion 3040 is shown in further detail in FIG. 31A. The proximalend of the sheath assembly 3004 may include a bifurcate 3016 (or Yconnector) that is coupled to the sheath 3012 by a luer fitting 3020.The bifurcate 3016 may comprise a tube 3028 extending in one direction(e.g., an axial direction) and another tube 3032 that extends in adirection offset from tube 3028. The tube 3028 may have an opening 3024through which a guidewire (not shown) may enter the proximal end of thesheath assembly 3004. The tube 3028 may also comprise a hemostasis valveat or adjacent the opening 3024. The guidewire is capable of extendingfrom the proximal end of the sheath assembly 3004 to the distal end ofthe sheath assembly 3004 through a lumen therein. The tube 3032 mayinclude a stopcock 3036 through which the liquid medium may enter thesheath assembly 3004.

Referring to FIG. 31A, FIGS. 31B, 31C and 31C′ there are depictedenlarged views of distal end portion 3040 of the sheath assembly 3004having a lumen 3024 there though. The distal end portion 3040 of thesheath assembly 3004 may comprise a sheath 3012 (or outer jacket), aninner liner 3096 radially or concentrically disposed within the sheath3012, an outer band 3072 disposed about the distal end of the sheath3012 (FIG. 31C), and a tapered tip 3076 disposed distally of the outerband 3072. The outer band 3072′ may alternatively be disposed integrallywithin the distal end of the sheath 3012′ such that the outer sheath (orjacket) 3012′ covers the (FIG. 31C′) outer band 3072′. The distal endportion 3040 of the sheath 3012 may also have an attenuating memberformed therein. The attenuating member may be included within the entirelength of the sheath 3012 or only at the distal end portion 3040.Assuming that the length of the sheath 3012 is 140 centimeters, thedistal end portion 3040 that includes the attenuating member may bebetween 0.010 and 10.0 centimeters in length, which represents between0.05 and 20.0 percent of the length of the sheath 3012.

The attenuating member may include a coil or coils 3068 integrallyformed from flat wire within the sheath 3012. An example of the flatwire is shown in FIG. 38, wherein the cross-sectional width (X) of theflat wire is 0.005 inches, and the cross-sectional height (Y) of theflat wire is 0.001 inches. The flat wire may be constructed of stainlesssteel, such as 304 stainless steel, or other type of metal or metalalloy. Additionally, it may be preferable for the flat wire to beconstructed with alternative dimensions, such as a cross-sectional width(X) of between 0.001 and 0.010 inches and a cross-sectional height (Y)of between 0.0005 and 0.015 inches. Alternatively, it may be preferableto use a round wire having a diameter between 0.0005 and 0.015 inches inlieu of a flat wire.

As discussed herein, it may be desirable for the ratio of the open areafor the attenuating member in comparison to the overall area of theattenuating member to be within a certain range, such as between 30percent to 70 percent, and possibly between 40 percent and 60 percent,and more possibly between 45 percent and 55 percent, such as 45, 46, 47,48, 49, 50, 51, 52, 53, 54 or 55 percent. Although round wire may beused to create the coil(s) 3068, using flat wire to construct thecoil(s) 3068 may provide the attenuating member with an overall thinnerlongitudinal cross-sectional profile while decreasing the amount of openarea per wrap of the wire because the height of the flat wire may besmaller than the width of the flat wire. The width of the flat wireprovides the desired ratio of open area for the attenuating member incomparison to the overall area of the attenuating member, while theheight of the material increases the coil(s) strength to withstand thelaser-induced pressure wave without breaking. In other words, a smallerlongitudinal cross-sectional profile reduces the overall diameter of thesheath assembly, thereby allowing the kit to enter smaller sizedvasculature, while maintaining sufficient strength and rigidity toabsorb and attenuate the laser-induced pressure wave.

There are three factors in determining the percentage of open area inthe attenuating member: (1) the width of the flat wire (or diameter ofthe round wire); (2) the number of wraps of the wire; and (3) the gapbetween each wrap of wire. Once two of these factors are determined fora desired percentage of open area in the attenuating member, the thirdfactor can be solved. In order to maintain a certain percentage of openarea in the attenuating member, there is an inverse relationship betweenthe number of wraps and the width of the flat wire (or diameter of theround wire). That is, for a certain percentage of open area in theattenuating member, the necessary wraps per inch decreases with a wirehaving a larger width, and the necessary wraps per inch increases with awire having a smaller width. Additionally, there is also an inverserelationship between the number of wraps per inch and the gap betweenthe wire wraps. That is, for a certain percentage of open area in theattenuating member using a predetermined wire size, the wraps per inchincreases with a smaller gap between the wire(s). Moreover, there is adirect relationship between the size of the gap between the wire and theamount of open area in the attenuating member. That is, for a given wirewidth, the greater the gap between each winding, the larger the openarea in the attenuating member, and the smaller the gap between eachwinding, the smaller the open area in the attenuating member.

For example, assuming that the attenuating member is constructed of0.005 inch wide by 0.001 tall inch flat wire with a desired open areabetween 30 percent and 70 percent, the attenuating member may includebetween about 75 and 125 wraps (or revolutions) per inch. Specifically,a gap of about 0.008 inches between each wrap of 0.005 inch wide flatwire produces an open area of about 61.5 percent, and a gap of about0.003 inches between each wrap of 0.005 inch wide flat wire produces anopen area of about 37.5 percent. Additionally, a gap of about 0.005inches between each wrap of 0.005 inch wide flat wire produces an openarea of about 50 percent. The attenuating member, therefore, may beconstructed from the flat wire such that the attenuating member includesbetween 75 and 125 wraps (or revolutions) per inch of the flat wire,between 80 and 120 wraps per inch of the flat wire, between 85 and 115wraps per inch of the flat wire, between 90 and 110 wraps per inch ofthe flat wire depending upon the amount of open area within theattenuating member, the size (i.e., width) of the wire and the gapbetween each wrap of the wire. As such, it may also be preferable forthe attenuating member to include about 75, 80, 85, 90, 95, 100, 105,110, 115, 120 or 125 wraps per inch of the flat wire, wherein the flatwire is wound such that the width (X) of the flat wire is parallel withthe longitudinal axis of the sheath 3012, and the height (Y) of the flatwire is perpendicular with the longitudinal axis of the sheath 3012.Additionally, if it desirable for the attenuating member to have adesired open area between 30 percent and 70 percent using a 0.004 inchwide flat wire, the gap between windings may be between, 0.0017 and0.0093 inches respectively. These are examples, which shall not limitthe scope of this disclosure because it may be desirable to have a flatwire with dimensions of 0.0002 to 0.010 inches wide and 0.0005 to 0.002inches high, as well as round wire having a diameter between 0.0005 to0.010 inches. For these ranges of wire size, the gap between the wirewinding(s) and the wraps per length (inch) can be adjusted accordinglyto produce the desired open area in the attenuating member.

Upon forming the sheath 3012 with the internally disposed attenuatingmember, the sheath 3012 may have an inner diameter between 0.010 and0.200 inches and an outer diameter of about 0.014 inches such that thewall thickness of the sheath 3012 is between 0.002 and 0.015 inches. Thesheath 3012 may be constructed of a polymeric material, such asNylon-12. As mentioned above, distal end portion 3040 may also includean inner liner 3096 radially or concentrically disposed within thesheath 3012. The inner liner 3096 may be constructed of a polymer suchas a polyimide having a thickness between 0.0005 and 0.010 inches, suchas 0.0005, 0.0006, 0.0007, 0.0008, 0.0009, 0.001, 0.0015, 0.002,0.00025, 0.003, 0.0035, 0.004, 0.0045, 0.005, 0.0055, 0.006, 0.0065,0.007, 0.0075, 0.008, 0.0085, 0.0090, 0.0095 and 0.010 inches.

Again, the distal end portion 3040 of the sheath assembly 3004 maycomprise an outer band 3072, which may also be referred to as a markerband, disposed about the distal end of the sheath 3012 and a tapered tip3076 disposed distally of the outer band 3072. The outer band 3072 maybe constructed of a highly radiopaque material, such as platinum iridiumalloy or polymers doped with radiopaque materials such as bariumsulfate, bismuth subcarbonate, bismuth trioxide, or tungsten. Thetapered tip 3076 may be constructed of the same material as the sheath3012 or an alternative material, such as pebax, polysulfone, HDPE, LDPE,UHMWPE, polypropylene, polyolefins, carbothane, polyurethane, Suralyn,ionomers, Estane, EPTFE, PTFE, or FEP. The tapered tip 3076 may,therefore, be formed integrally with the sheath 3012 or as a separatecomponent. The circumference of the tapered tip 3076 may taper radiallyinward from its proximal end to its distal end between 1 degree and 10degrees, such as 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 degrees.

It may also be preferable for the inner diameter of the tapered tip 3076to be slightly less than the inner diameter of the inner liner 3096 ofthe sheath 3012, particularly if the inner liner 3096 is omitted fromthe distal end 3040 of the sheath assembly 3004. For example, it may bepreferable for the tapered tip 3076 to seal the interface between thesheath assembly 3004 and the laser catheter assembly 3008 such that theescape of the liquid medium at the distal end of the kit 3000 isminimized or reduced. If a 5 French sized laser catheter 3080 of thelaser catheter assembly 3008 has an outer diameter of about 0.056inches, then it may be preferable for the inner diameter of the taperedtip 3076 to be about 0.057 inches, thereby leaving a radial distance orgap of about 0.0005 inches between the laser catheter 3080 and thetapered tip 3076. For the purposes of this disclosure about 0.0005inches means 0.0001 to 0.001 inches. Additionally, if a 6 French sizedlaser catheter 3080 of the laser catheter assembly 3008 has an outerdiameter of about 0.069 inches, then it may be preferable for the innerdiameter of the tapered tip 3076 to be about 0.070 inches, therebyleaving a distance or gap of about 0.0005 inches between the lasercatheter 3080 and the tapered tip 3076. Although the embodimentsdescribed above includes a gap of about 0.0005 inches between the lasercatheter 3080 and the tapered tip 3076, such gap may be between 0 and0.002 inches and still perform a sufficient seal.

The gap between the laser catheter 3080 and the inner liner 3096 (of thesheath 3012) will preferably be greater than the gap between the lasercatheter 3080 and tapered tip 3076, thereby allowing the liquid mediumto enter such gap between the laser catheter 3080 and the inner liner3096. For example, for a 5 French sized laser catheter 3080 of the lasercatheter assembly 3008 having an outer diameter of about 0.056 inches,it may be preferable for the inner diameter of the inner liner 3096 tobe about 0.0615 inches, thereby leaving a radial distance or gap ofabout 0.00275 inches between the laser catheter 3080 and the inner liner3096, which is about five times the gap between the gap between thelaser catheter 3080 and the tapered tip 3076. For a 6 French sized lasercatheter 3080 of the laser catheter assembly 3008 having an outerdiameter of about 0.069 inches, it may be preferable for the innerdiameter of the inner liner 3096 to be about 0.0745 inches, therebyleaving a distance or gap of about 0.00275 inches between the lasercatheter 3080 and the inner liner 3096, which is about five times thegap between the gap between the laser catheter 3080 and the tapered tip3076. Accordingly, the diameter of the lumen in the inner liner 3096 isgreater than the diameter of the lumen in the tapered tip 3076. Althoughthe embodiments described above includes a radial gap of about 0.00275inches between the laser catheter 3080 and the inner liner 3096, suchradial gap may be between about 0.001 and 0.010 inches and still providea sufficient amount of liquid medium to enter the radial gap and createthe desired pressure wave upon exposure to the laser light energy.

Referring to FIG. 32 and FIG. 32A, there is depicted the laser catheterassembly 3008 shown in FIG. 30. An example of the laser catheterassembly 3008 is the Turbo-Elite™ laser atherectomy catheter produced byThe Spectranetics Corporation. The laser catheter assembly 3008 mayinclude a laser catheter 3080, a bifurcate 3044, a luer adapter 3048,another sheath 3052 and a coupler 3056. Coupler 3056 is coupled to alaser system, such as the CVX-300 Excimer Laser System, which is alsoproduced by The Spectranetics Corporation. The sheath 3052 is coupled tothe coupler 3056, and sheath 3052 encapsulates the fiber optic bundle,which passes through the bifurcate 3044 and the laser catheter 3080. Thecoupler 3056 is configured to encapsulate or incorporate the fiber opticbundle. The bifurcate 3044 may be coupled to the proximal end of thesheath 3080. Additionally, luer adapter 3048 may also be coupled to theproximal end of the bifurcate 3044, thereby providing an entry point tofor a guidewire to enter into and pass through the laser catheterassembly 3008. The distal portion 3060 of the laser catheter assembly3008 may include a radiopaque outer band 3084 and emitters 3088 disposeddistally of the radiopaque outer band 3084, wherein the emitters 3088are the distal ends of the optical fibers or coupled to the opticalfibers.

Referring to FIG. 33, there is depicted a flow chart illustrating thesteps of a method 3300 of using, for example, the kit 3000 (depicted inFIG. 30) that includes the laser catheter assembly 3008 (depicted inFIG. 32) and the sheath assembly 3004 (depicted in FIG. 31) to removeplaque buildup or occlusive disease by performing an atherectomyprocedure and treating the remainder of the vascular occlusion withinthe intima using the laser catheter assembly 3008 in conjunction withthe sheath assembly 3004 to create laser-induced pressure waves in thepresence of a liquid medium and disrupt a portion of the vascularocclusion. This method 3300 may be used to treat coronary arteriesand/or peripheral arteries including but not limited to arteries of thevasculature of the legs, the renal arteries, subclavian arteries, etc.The method 3300 in FIG. 33 includes locating a vascular occlusion in thevasculature (or blood vessel) of a subject at step 3305. The next step3310, which is optional, includes locating the guidewire 3092 at thevascular occlusion and/or inserting the guidewire 3082 through thevascular occlusion or through the passageway past the vascularocclusion. Step 3315 includes inserting an atherectomy device over theguidewire 3092 and into the patient's vasculature. One type ofatherectomy device is an ablation catheter, such as the laser catheterassembly 3008 discussed herein, which is capable of ablating at least aportion of the vascular occlusion. Other types of ablation cathetersinclude radiofrequency ablation catheters, microwave ablation catheters,and cryoablation catheters. Atherectomy devices other than ablationcatheters, such as mechanical atherectomy devices, may also be used toremove the vascular occlusion. Assuming that the laser catheter assembly3008 is used as the atherectomy device, the sheath assembly 3004 mayalso be introduced to the patient's vasculature either simultaneouslywith the laser catheter assembly 3008 or sequentially, such as prior toor after introducing the laser catheter assembly 3008 into the patient'svasculature.

Once the laser catheter assembly 3008 and the sheath assembly 3004,particularly the laser catheter 3080 and the sheath 3012, respectively,are located within the patient's vasculature, the laser catheter 3080 ispositioned beyond the distal end of the sheath 3012 and adjacent thevascular occlusion at step 3320. The clinician using the kit 3000 willbe able to determine that the laser catheter assembly 3008, particularlythe emitters 3088 is positioned beyond the distal end 3040 of the sheathassembly 3004 and adjacent the vascular occlusion because the radiopaqueouter band 3084 of the laser catheter 3080 will be illustrated underfluoroscopy as being distal of the outer band 3072 of the sheathassembly 3004, as illustrated in FIG. 30A. At this point, step 3325 maybe initiated by activating the emitters 3088, such as supplying laserlight energy thereto, and ablating the vascular occlusion (or a portionthereof), as illustrated in FIG. 26G, FIG. 26H and/or FIG. 26H′, whereinthe laser catheter assembly 3008 and the sheath assembly 3004 replacethe sheath 1120 and the catheter 1010, respectively, in FIG. 26G, FIG.26H and/or FIG. 26H′.

After the vascular occlusion (or a portion thereof) is removed from thevasculature, step 3330 may then be performed. Step 3330 includespositioning the sheath assembly 3004 over the laser catheter assembly3008, particularly the sheath 3012 over the laser catheter 3080, withinvasculature of a subject and adjacent the vascular occlusion similar tothe way in which the sheath 1120 and the catheter 1010 are situated inFIG. 26H′. The axial locations of the laser catheter 3080 and the sheath3012 may be adjusted by translating either or both components withrespect to one another back and forth between the positions illustratedin FIG. 26H and FIG. 26H′ or any position(s) therebetween. For purposesof clarification, FIGS. 30A and 30B correspond to how the laser catheterassembly 3040 and the sheath assembly 3004, particularly the lasercatheter 3080 and the sheath 3012, of those figures would be oriented inthe vasculature if the catheter 1010 and sheath 1120 of FIG. 26H, andFIG. 30B′ corresponds to how the laser catheter 3080 and the sheath 3012of that figure would be oriented in the vasculature, if the catheter1010 and sheath 1120 of FIG. 26H′ would be replaced with the lasercatheter 3080 and the sheath 3012. Particularly, the axial locations ofthe laser catheter 3080 and the outer sheath 3008 may be axially alignedsuch that the emitters 3088 are within the attenuating member 3068 ofthe sheath 3012, and the corresponding portions of the sheath 3012 andattenuating member 3068 are adjacent the vascular occlusion (orremainder thereof). That is, step 3330 includes positioning the sheath3012 over a laser catheter 3080 within the vasculature of a subject andadjacent the vascular occlusion such that distal end 3060 of the lasercatheter assembly 3008, including its emitters 3088, are within thedistal end 3040 of the sheath assembly 3008 such that the emitters 3088are within the attenuating member 3068 of the sheath assembly 3004, andthe outer band 3084 of the laser catheter assembly 3008 is proximal ofthe radiopaque outer band 3072 of the sheath assembly 3004, as depictedif FIG. 30B′ (and FIG. 26H′).

Once the distal portions 3040, 3060 of the sheath assembly 3004 andlaser catheter assembly 3008 are disposed adjacent the vascularocclusion, such that the emitters 3088 and the attenuating member 3068are axially aligned adjacent the vascular occlusion, the liquid mediummay be introduced to the distal end 3060 of the laser catheter assembly3008 as set forth in step 3335 of FIG. 33. The liquid medium may beintroduced to the kit 3000 through the tube 3032 and/or stopcock 3036 atthe proximal end of the sheath assembly 3004. Continuing to refer toFIG. 33, step 3340 includes activating an energy source, such as alaser, to create laser-induced pressure waves in the presence of theliquid medium and disrupting a portion of the vascular occlusion. Thedistal ends 3040, 3060 of the laser catheter assembly 3008 and thesheath assembly 3004 may be used to traverse the entire vascularocclusion or only disrupt a portion of the vascular occlusion. That is,the laser catheter assembly 3008 and the sheath assembly 3004,particularly their respective distal portions 3040, 3060 may moveaxially with respect to another and/or together, while emittinglaser-induced pressure waves to disrupt a portion of the vascularocclusion. While activating the emitters 3088, it may be desirable totranslate the laser catheter assembly 3008 within the sheath assembly3004 while the sheath assembly 3004 remains stationary, as the liquidmedium continues to be introduced to the distal end 3010 of the kit3000. For example, it may be desirable to retract the laser catheterassembly 3008 within the sheath assembly 3004 by axially moving thelaser catheter assembly 3008 within the sheath assembly 3004 in aproximal direction at a rate of between 0.5 mm/second and 5 mm/second,particularly at a rate of less than or equal to 4.5, 4.0, 3.5, 3.0, 2.5,2.0, 1.5 or 1 mm/second. In addition to moving the laser catheterassembly 3008 within the sheath assembly 3004 in a proximal direction,the laser catheter assembly 3008 may move in a distal direction withinthe sheath assembly 3004 while maintaining the emitters 3088 proximal ofthe distal end 3040 of the sheath assembly 3008. For the purposes ofclarification, during emitter activation, as well as proximal and distalmovement of the sheath assembly 3008 to disrupt the calcium, theemitters 3088 are within the distal end 3040 of the sheath assembly 3008such that the emitters 3088 are within the attenuating member 3068 ofthe sheath assembly 3004, and the outer band 3084 of the laser catheterassembly 3008 is proximal of the radiopaque outer band 3072 of thesheath assembly 3004.

During disruption of the calcium, it may be desirable to adjust thesettings of the laser system to which the laser catheter assembly 3008is coupled such that the emitters 3088 produce a fluence between 30 and80 mJ/mm², more preferably between 40 and 70 mJ/mm², and even morepreferably at a fluence of 45, 50, 55, 60 mJ/mm². It may also bedesirable for the repetition rate of the laser to be between 25 hertzand 80 hertz, including 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75 and80 hertz. It may also be desirable for the pulse width of the laser tobe between 125 nanoseconds and 200 nanoseconds, including 125, 130, 135,140, 145, 150, 155, 160, 165, 170, 175, 180, 185, 190, 195 and 200nanoseconds. As also discussed herein, the wavelength of the laser lightenergy and that emitted by the emitters may include a variety ofwavelengths, including a wavelength of between about 150 nanometers toabout 400 nanometers such as 308 nanometers.

If the laser catheter assembly 3008 and the sheath assembly 3004 arecontinued to be used to disrupt a portion of the vascular occlusion,then laser catheter assembly 3008 and sheath assembly 3004 are used asset forth in step 2740. If, however, the clinician wishes to discontinueusing the laser catheter assembly 3008 and the sheath assembly 3004 todisrupt a portion of the vascular occlusion and use the laser catheterassembly 3008 to perform additional ablation, then the clinician repeatsstep 3320 (as well as the additional subsequent steps), as depicted inFIG. 33, and the distal portion 3060 of laser catheter assembly 3008 isagain extended beyond the distal portion 3040 of the sheath assembly3004, as illustrated in FIGS. 30A and 30B (and FIG. 26G, FIG. 26H and/orFIG. 26H′). Upon satisfactory ablation and disruption of the vascularocclusion by repeating steps 3320 to 3340 or 3345, activation of theemitters and introduction of the liquid medium to the kit 3000 isdiscontinued and the kit is removed from the patient's vasculature.

As discussed above, transmitting pulses of light energy from an emitterinto a liquid medium creates laser-induced pressure waves and/or vaporbubbles and additional resultant pressure waves that disrupt at least aportion of a vascular occlusion. The catheter may include a guidewirelumen through which a guidewire can pass and cross the vascularocclusion. It may also be desirable to excite and vibrate the guidewireto increase the guidewire's ability to pierce and cross the vascularocclusion. Accordingly, the present disclosure also contemplatesdirecting the laser light energy emitted by the emitter into the liquidmedium in a direction which causes the liquid medium to propagatelaser-induced pressure waves toward the guidewire lumen and/or guidewiresuch that the laser-induced pressure waves excite and vibrate theguidewire.

Although the method illustrated in FIG. 33 depicts steps 3305 through3350 of method 3300 as being performed serially, any or all of the stepswithin the method 3300 may in any order and/or in parallel with any ofthe other steps. For example, certain steps can be performed withoutperforming other steps. Upon completing step 3335 and/or step 3340, thecombined laser catheter and sheath can optionally be repositioned withinthe vasculature and adjacent another portion thereof. Similarly, uponcompleting step 3335 and/or step 3340, the emitter(s) can optionally berepositioned within the sheath. The sheath can be repositioned withinthe vasculature and/or the emitter(s) can be repositioned within thesheath.

Similar to how the laser catheter assembly 3008 and the sheath assembly3004 of FIGS. 30-32 can replace the catheter 1010 and sheath 1120 shownin FIGS. 26G, 26H and FIG. 26H′ to perform the method of FIG. 33, whichis similar to the method of FIGS. 27A and 27B, to perform an atherectomyfollowed by disruption of the remaining portion of the vasculatureocclusion, the laser catheter assembly 3008 and the sheath assembly 3004of FIGS. 30-32, particularly the laser catheter 3080 and the sheath3012, respectively, can replace the catheter 1010 and sheath 1120 shownin FIG. 28C to perform the method of FIG. 33, which is similar to themethod of FIGS. 27A and 27B, to perform the method of depicted in FIG.29. As set forth above, FIG. 29 illustrates a method using a kit 3000 togenerate laser-induced pressure waves to treat the calcium deposits inthe tissue (e.g., media) and/or tissue layers (e.g., media layer) of theblood vessel by disrupting the calcium deposits to increase vasculaturecompliance, thereby increasing blood flow therethrough.

Referring to FIGS. 34A and 34B, there are depicted enlarged views of adistal portion of another kit that includes a the distal portion of thelaser catheter assembly 3008 and an alternative embodiment of the distalportion sheath assembly 3004 in comparison to the sheath assembly 3004in FIGS. 30-31. Similar to the distal portion of the sheath assembly3004 in FIGS. 30-31, which comprises a sheath 3012 (or outer jacket)with an attenuating member formed therein, an inner liner 3096 radiallyor concentrically disposed within the sheath 3012, an outer band 3072disposed about the distal end of the sheath 3012, and a tapered tip 3076disposed distally of the outer band 3072, the distal end portion of thesheath assembly depicted in FIGS. 34A and 34B, may also have a sheath3412 (or outer jacket) with an attenuating member (not shown) formedtherein, an inner liner (not shown) radially or concentrically disposedwithin the sheath 3412, an outer band 3472 disposed about the distal endof the sheath 3412, and a tapered tip 3476 disposed distally of theouter band 3472. The tapered tip 3476 may have multiple sections, suchas a proximal section 3480, an intermediate section 3484 and a distalsection 3488. The length of some or all of the sections may the same ordifferent. For example, in FIGS. 34A and 34B, the length of the proximalsection 3480 is longer than both the intermediate section 3484 and thedistal section 3488, but the intermediate section 3484 is shorter thanthe distal section 3488. Additionally, some or all of the sections maybe tapered. For example, in FIGS. 34A and 34B, the proximal section 3480is tapered radially inward from its proximal end to its distal end, theintermediate section 3484 is tapered and the distal section 3488 is nottapered. The sections may be tapered between 1 degree and 10 degrees,such as 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 degrees. The internal diameterof sections may be the same or different, but it is be preferable forthe inner diameter of the distal section 3488 of the tapered tip 3476 tobe the smallest and similar to the size of the internal diameter of thetapered tip 3076 in FIGS. 30 and 31. For example, in FIGS. 34A and 34B,the proximal section 3480 has the largest internal diameter, theintermediate section 3484 has the next largest diameter and the internaldiameter of the distal section 3488 is equal to or less than theinternal diameter of the intermediate section 3484.

Depending upon the length of the tapered tip 3476, it may be preferablefor the distal end of the distal section 3488 to also include aradiopaque marker 3478, similar to outer band 3472. Including radiopaqueouter band 3472 at or proximate the proximal section 3480 of the taperedtip 3476 and a radiopaque marker at the distal end of the distal section3488 allows a clinician to know whether the distal end of the lasercatheter assembly 3008, particularly the outer band 3084 and theemitters 3088 are proximal to both the tapered tip 3476, within thetapered tip 3476 or distal of the tapered tip 3476. This may beparticularly helpful when a clinician is alternating between translatingthe laser catheter beyond and within the outer sheath, such as switchingbetween performing an atherectomy procedure and activating the emittersto disrupt a portion of the occlusion or calcium within vasculature.

As mentioned above, the length of some or all of the sections of thetapered tip may be the same or different. For example, FIG. 35 is anenlarged view of a distal portion of another kit that includes a lasercatheter assembly 3008 and an alternative embodiment of the sheathassembly, wherein the sheath assembly has an outer sheath 3512 and atapered tip 3576 comprising a proximal section 3580, an intermediatesection 3584 and a distal section 3588 of about equal lengths, therebyincreasing the overall length of the tapered tip 3576 in comparison tothe overall length of the tapered tip 3476 in FIGS. 34A and 34B. Similarto outer sheath in FIGS. 34A and 34B, the outer sheath in FIG. 35 alsoincludes a radiopaque outer band 3572 at or proximate the proximalsection 3580 of the tapered tip 3576 and a radiopaque marker 3578 at thedistal end of the distal section 3588 of the tapered tip 3576.

Referring to FIGS. 36A and 36B, there are depicted enlarged views of adistal portion of a kit that includes a laser catheter assembly 3008 andan alternative embodiment of the distal portion of the sheath assembly,wherein the sheath assembly has an outer sheath 3612 and a convex-shapedtapered tip 3676 disposed distally of the outer sheath 3612. As shown inthese figures, the convex-shaped tapered tip 3676 has an increasingvarying pitch angle from its proximal end to its distal end. The outersheath 3612 also may also have a radiopaque outer band 3672 at theproximal end of the tapered tip 3676 and a radiopaque marker 3678 at thedistal end of the tapered tip 3676. FIG. 36A depicts the distal end andemitter(s) of the laser catheter assembly 3008 is a position proximalthe tapered tip 3676 and the radiopaque outer band 3672. FIG. 36Bdepicts the distal end and emitter(s) of the laser catheter assembly3008 is a position distally of the proximal end of the tapered tip 3676and proximal the distal end of the tapered tip 3676, such that thedistal end and emitter(s) of the laser catheter assembly 3008 areradially aligned within tapering portion of the tapered tip 3676. Thematerial from which the tapered tip 3676 is constructed may include anon-expandable or radially expandable material to allow for the innerdiameter of the tapered tip 3676 to expand as the laser catheterassembly 3008 translates distally into the tapered tip 3676. Thematerial of the tapered tip 3676 may be sufficiently flexible so thatthe radially expandable material allows the inner diameter of thetapered tip 3676 to expand to a diameter that allows the distal end andemitter(s) of the laser catheter assembly 3008 to extend beyond thedistal end of the tapered tip 3676, while simultaneously sealing theinterface between the laser catheter and outer sheath, therebyminimizing or preventing the escape or leakage of any liquid mediumtherebetween.

Referring to FIGS. 37A and 37B, there is depicted is an enlarged view ofa distal portion of another kit that includes a laser catheter assembly3008 and an alternative embodiment of the outer sheath 3712. Rather thanhaving a tapered distal tip as shown in FIGS. 34, 35 and 36, the tip3776 in FIGS. 37A and 37B may be the same size at its proximal end anddistal end and have a constant outer diameter and inner diameter alongthe length of the tip 3776. The inner diameter of the tip 3776 is a sizethat cooperates to seal the interface between the tip 3776 of the sheathassembly and the laser catheter assembly 3008 as the distal portionsthereof.

Referring to FIGS. 39 and 39A, there is depicted an outer sheathassembly 3904 for a kit (not shown) that further includes a bifurcate(such as the bifurcate or Y connector 3016) and a laser catheterassembly (such as the laser catheter assembly 3008). The sheath assembly3904 may include a luer fitting 3920 at a proximal end portion fordetachably coupling to the bifurcate. The sheath assembly 3904 mayfurther include a distal end portion 3940 and an outer sheath 3912having a working length of about between 50 cm and 200 cm, including 140cm, and a lumen 3924 extending between such ends. The outer sheath 3912of FIGS. 39, 39A and 40 may be used in alternative to outer sheath 3012in FIGS. 30 and 31 discussed hereinabove.

Referring now to FIGS. 39A and 40, there are depicted an enlarged viewof the distal end portion 3940 of the sheath assembly 3904 and apartially exploded view illustrating various layers of the sheath 3912,respectively. The distal end portion 3940 of the sheath assembly 3904may include a tapered tip 3976, an outer band 3972 disposed proximallyfrom the tapered tip 3976 and disposed about the distal end of thesheath 3912, and the distal end of the sheath 3912.

The tapered tip 3976 may be constructed of various materials, such aspebax, polysulfone, high-density polyethylene (HDPE), low-densitypolyethylene (LDPE), ultra-high-molecular-weight polyethylene (UHMWPE),polypropylene, polyolefins, carbothane, polyurethane, Suralyn, ionomers,Estane, expanded polytetrafluoroethylene (EPTFE),polytetrafluoroethylene (PTFE), or fluorinated ethylene propylene (FEP).The tapered tip 3976 may be formed integrally with the sheath 3912 or asa separate component. The circumference of the tapered tip 3976 maytaper radially inward from its proximal end to its distal end between 1degree and 10 degrees, such as 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 degrees.It may be preferable for the tapered tip 3976 to have an inner diameterthat facilitates sealing the interface between the sheath assembly 3904and the laser catheter assembly such that the escape of the liquidmedium at the distal end of the kit is minimized or reduced. If a 6French sized laser catheter of the laser catheter assembly has an outerdiameter of about 0.069 inches, then it may be preferable for the innerdiameter of the tapered tip 3976 to be about 0.058 inches. If a 7 Frenchsized laser catheter of the laser catheter assembly is to be used, itmay be preferable for the inner diameter of the tapered tip 3976 to beabout 0.071 inches. If an 8 French sized laser catheter of the lasercatheter assembly is to be used, it may be preferable for the innerdiameter of the tapered tip 3976 to be about 0.082 inches.

The outer band 3972, which may also be referred to as a marker band, maybe constructed of a highly radiopaque material, such as platinum iridiumalloy or polymers doped with radiopaque materials such as bariumsulfate, bismuth subcarbonate, bismuth trioxide, or tungsten.

Referring specifically to FIG. 40, the sheath 3912 includes an outerjacket 3978 that covers the outer band 3972 (not shown). The sheath 3912further includes an attenuating member 3968 radially or concentricallydisposed within the outer band 3972, an intermediate layer 3970 radiallyor concentrically disposed within the attenuating member 3968, and aninner liner 3996 radially or concentrically disposed within theintermediate layer 3970. Proximally from the outer band 3972, the sheath3912 includes a similar structure. Specifically, the attenuating member3968 is radially or concentrically disposed within the outer jacket3978, the intermediate layer 3970 is radially or concentrically disposedwithin the attenuating member 3968, and the inner liner 3996 is radiallyor concentrically disposed within the intermediate layer 3970. In someembodiments, the attenuating member 3968 is only present at the distalend portion 3940. Assuming that the length of the sheath 3912 is 140centimeters, the distal end portion 3940 that includes the attenuatingmember 3968 may be between 0.010 and 10.0 centimeters in length, whichrepresents between 0.05 and 20.0 percent of the length of the sheath3912.

The outer jacket 3978 may be constructed of various materials, such aspebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene, polyolefins,carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE, PTFE, orFEP. If a 6 French sized laser catheter of the laser catheter assemblyis to be used, the outer jacket 3978 may provide the sheath 3912 with anouter diameter between 0.058 and 0.098 inches, such as 0.058, 0.062,0.066, 0.070, 0.074. 0.078, 0.082, 0.086, 0.090, 0.094, and 0.098inches. If a 7 French sized laser catheter of the laser catheterassembly is to be used, the outer jacket 3978 may provide the sheath3912 with an outer diameter between 0.071 and 0.111 inches, such as0.071, 0.075, 0.079, 0.083, 0.087, 0.091, 0.095, 0.099, 0.103, 0.107,and 0.111 inches. If an 8 French sized laser catheter of the lasercatheter assembly is to be used, the outer jacket 3978 may provide thesheath 3912 with an outer diameter between 0.082 and 0.122 inches, suchas 0.082, 0.086, 0.090, 0.094, 0.098, 0.102, 0.106, 0.110, 0.114, 0.118,and 0.122 inches. The outer jacket 3978 may have a wall thicknessbetween 0.0015 and 0.0035 inches, such as 0.0015, 0.0017, 0.0019,0.0021, 0.0023, 0.0025, 0.0027, 0.0029, 0.0031, 0.0033, and 0.0035.

The attenuating member 3968 is a braided structure 3968. The braidedstructure 3968 may include between 4 and 28 carriers and moreparticularly between 12 and 20 carriers, such as 12, 13, 14, 15, 16, 17,18, 19, or 20 carriers. Each carrier may include between 1 and 10 wires,such as 1, 2, 3, 4, 5, 6, 7, 8, 9, and 10 wires. Each wire may have across-sectional height between 0.0005 and 0.005, such as 0.0005, 0.0007,0.0009, 0.001, 0.002, 0.003, 0.004, and 0.005. Each wire may be a flatwire having a cross-sectional width between 0.0005 and 0.003, such as0.0005, 0.0007, 0.0009, 0.001, 0.002, and 0.003. Each wire may beconstructed of stainless steel, such as 304 stainless steel, or othertype of metal or metal alloy. The braided structure 3968 may have abraid density between 20 and 100 picks per inch (PPI) and particularlybetween 40 and 80 PPI, such as 40, 44, 48, 52, 56, 60, 64, 68, 72, 76,and 80 PPI. The relationship between the open area and the closed area(or the ratio of the open area to the overall area) within the braidedstructure 3968 should be such that a sufficient amount of laser-inducedpressure waves pass through the braided structure 3968, and the openarea should allow the laser-induced pressure waves to pass therethrough,while also limiting the size of the vapor bubbles that can form on theexterior of the sheath 3912. The braided structure 3968 may have an openarea between 45 percent and 85 percent, and possibly between 55 percentand 75 percent, such as 55, 56, 57, 58, 59, 60, 61, 62, 63, 64, 65, 66,67, 68, 69, 70, 71, 72, 73, 74, or 75 percent. The open area of thebraided structure depends on the braid density, the number of carriersin the braided structure 3968, the number of wires in each carrier, andthe dimensions of the wires.

The intermediate layer 3970 may be constructed of various materials,such as pebax, polysulfone, HDPE, LDPE, UHMWPE, polypropylene,polyolefins, carbothane, polyurethane, Suralyn, ionomers, Estane, EPTFE,PTFE, or FEP. The intermediate layer 3970 may have a wall thicknessbetween 0.0005 and 0.0025 inches, such as 0.0005, 0.0007, 0.0009,0.0011, 0.0013, 0.0015, 0.0017, 0.0019, 0.0021, 0.0023, and 0.0025.

The inner liner 3996 may be constructed of various materials, such as apolyamide or a fluoropolymer, specifically Neoflon FEP NP-101 availablefrom Daikin America. If a 6 French sized laser catheter of the lasercatheter assembly is to be used, the inner liner 3996 may provide thesheath 3912 with an inner diameter between 0.040 and 0.080 inches, suchas 0.044, 0.048, 0.052, 0.056, 0.060, 0.064, 0.068, 0.072, 0.076 and0.080 inches. If a 7 French sized laser catheter of the laser catheterassembly is to be used, the inner liner 3996 may provide the sheath 3912with an inner diameter between 0.053 and 0.093 inches, such as 0.053,0.057, 0.061, 0.065, 0.069, 0.073, 0.077, 0.081, 0.085, 0.089, and 0.093inches. If an 8 French sized laser catheter of the laser catheterassembly is to be used, the inner liner 3996 may provide the sheath 3912with an inner diameter between 0.064 and 0.104 inches, such as 0.064,0.068, 0.072, 0.076, 0.080, 0.084, 0.088, 0.092, 0.096, 0.100, and 0.104inches. The inner liner 3996 may have a wall thickness between 0.0005and 0.0025 inches, such as 0.0005, 0.0007, 0.0009, 0.0011, 0.0013,0.0015, 0.0017, 0.0019, 0.0021, 0.0023, and 0.0025.

Kits including the sheath assembly 3904 can be used to perform any ofthe methods described herein. In some embodiments, the sheath assembly3904 is capable of resisting damage for a duration of at least 1, 2, 3,4 or 5 minutes (or any duration therebetween) when laser pulses areemitted by a laser catheter during performance of such methods. Morespecifically, the sheath 3904 is capable of resisting damage when usingSpectranetics 1.4, 1.7, and 2.0 Turbo-Elite™ and 2.0 Turbo-Power™ lasercatheters to emit laser pulses at 60 fluence and 25 Hz into a contrastmedium of fifty percent (50%) Optiray 320 contrast with saline, infusedto the sheath 3904 at 5 mL/min. To facilitate this capability, one orboth of the outer jacket 3978 and the intermediate layer 3970 may beintegrally formed with the braided structure 3968 (that is, formed inmanner that causes one or both of the outer jacket 3978 and theintermediate layer 3970 to occupy at least some of the open area of thebraided structure). For example, the inner liner 3996 may be extruded,the intermediate layer 3970 may be over-extruded on the inner liner3996, the braided structure 3968 may be positioned over the intermediatelayer 3970, and the outer jacket 3978 may be over-extruded on thebraided structure 3968. The sheath 3912 is laminated, coupled to theluer fitting 3020, and the outer jacket 3978 may be stripped at thedistal end of the sheath 3912.

In comparison to conventional unreinforced and/or reinforced sheaths,such as in comparison to sheath assemblies that include various ormultiple laminated layers or sheath assemblies using other manufacturingprocesses, the sheath assembly 3904 disclosed and discussed herein withrespect to FIGS. 39-41 is susceptible to less damage when used inconjunction with a laser catheter and laser pulses are emitted into acontrast medium within such sheath assemblies over short or extendeddurations, particularly durations in which continues emission of laserpulses occurs for more than 20 seconds, 40 seconds, 1 minute and/or 2minutes. Minimizing and/or preventing the sleeve from such potentialdamage, such as bulging, splitting, or delaminating (in the event thesleeve comprises multiple layers), forming a whole within the sleeve, inturn, reduces the possibility of a surgeon experiencing increaseddifficulty while translating the sleeve through the patient'svasculature and/or translation relative to the laser catheter.

Referring to FIG. 41, a laser catheter system 4010 or kit generallyincludes a laser catheter 4012, a sheath 4014, and a handle 4016 thattranslatably couples the laser catheter 4012 to the sheath 4014. Thelaser catheter 4012 and the sheath 4014 may be similar to, for example,the components of the two-piece catheter systems or kits describedherein. As a specific example, the laser catheter 4012 and the sheath4014 may be similar to the components described above in connection withFIGS. 11A-11D. The laser catheter 4012 is translatably disposed within alumen of the sheath 4014 and the handle 4016. The laser catheter 4012includes a lumen (shown elsewhere) for translatably receiving aguidewire (shown elsewhere).

A liquid medium is introduced into the sheath 4014 distal to the lasercatheter 4012, particularly distal to the optical fibers/emitters (shownelsewhere) of the laser catheter 4012 such that when the laser isactivated, the liquid absorbs the light and creates laser-inducedpressure waves and/or vapor bubbles and resultant pressure waves. Theliquid is introduced via the lumen between the laser catheter 4012 andthe sheath 4014, which in turn receives the liquid from a proximal portof the handle 4016 coupled to the sheath 4014.

Referring now to FIGS. 41 and 42, the handle 4016 of the laser cathetersystem 4010 includes a treatment mode selection system 4018. Thetreatment mode selection system 4018 receives an input from a user andthen configures the laser catheter system 4010 for use in differenttypes of procedures. For example, the treatment mode selection system4018 may configure the laser catheter system 4010 to a firstconfiguration for use in a first type of treatment and a secondconfiguration for use in a second type of treatment. In the firstconfiguration, the distal end of the laser catheter 4012 is disposeddistally relative to the distal end of the sheath 4014. As such, thesystem is configured to perform an atherectomy procedure, such as theatherectomy procedure shown in FIG. 27A at Step 2715 and described inassociated portions of the description, the atherectomy procedure shownin FIG. 26G and described in the associated portions of the description,or the like. In the second configuration, the distal end of the lasercatheter 4012 is disposed in the lumen proximally relative to the distalend of the sheath 4014. As such, the system is configured to perform aprocedure in which the system creates laser-induced pressure waves inthe presence of a liquid medium to thereby disrupt a portion of avascular occlusion, such as the procedure shown in FIGS. 27A and 27B atSteps 2730 and 2725 and described in the associated portions of thedescription, the procedure shown in FIG. 26H′ and described in theassociated portions of the description, or the like. In someembodiments, the treatment mode selection system 4018 may configure thelaser catheter system 4010 to additional configurations or alternativeconfigurations.

The treatment mode selection system 4018 includes a controller 4020 thatis in operative communication with a user input 4022, and the controller4020 receives a signal from the user input 4022. In some embodiments andas illustrated in FIG. 41, the user input 4022 may include atranslatable button 4024 that actuates a contact switch (not shown) tosend signals to the controller 4020. Based on the signal, the controller4020 configures the laser catheter system 4010 for use in differenttypes of procedures as described above. More specifically, thecontroller 4020 translates the laser catheter 4012 relative to thesheath 4014 via a prime mover 4026 (for example, a linear actuator, arotary actuator, or the like) to facilitate using the laser cathetersystem 4010 in different types of procedures.

In some embodiments, the controller 4020 is in operative communicationwith one or more valves 4028, and actuating the user input 4022 causesthe controller 4020 to send signals to and thereby actuate the valves4028. The valves 4028 thereby deliver one or more liquid media to thelumen of the sheath 4014 (for example, a contrast medium, saline, atherapeutic agent, and other liquid media described herein) asappropriate for specific types of procedures.

In some embodiments, the controller 4020 is in operative communicationwith a laser generator 4030 coupled to the laser catheter 4012, andactuating the user input 4022 causes the controller 4020 to send signalsto and thereby configure one or more operating parameters of the lasergenerator 4030 (for example, pulse frequency, fluence, and the like) toappropriate values for specific types of procedures.

In some embodiments, the controller 4020 is in operative communicationwith sensors (not shown) coupled to the laser catheter 4012 which canidentify the parameters of the laser generator 4030 (for example, pulsefrequency, fluence, and the like) without direct communication with thelaser generator 4030 and modify those parameters through operationscontrolled and contained within the treatment mode selection system4018.

In some embodiments, the controller 4020 is in operative communicationwith sensors (not shown) coupled to the laser catheter 4012 which canidentify the parameters of the laser generator 4030 (for example, pulsefrequency, fluence, and the like) without direct communication with thelaser generator 4030 and actuate the prime mover 4026 and or the valves4028 of the treatment mode selection system 4018.

The laser catheter system 4010 further includes a power supply 4032 (forexample, a battery) that provides power to the controller 4020, theprime mover 4026, and/or the valves 4028.

In some embodiments and as shown in FIG. 41, the treatment modeselection system 4018 includes a second translatable button 4034. Insome embodiments, the second translatable button 4034 may be actuated bya user to move the laser catheter 4012 to the first configuration, thesecond configuration, and an infinite number of configurationstherebetween. In some embodiments, the first translatable button 4024may be actuated to configure one or more operating parameters of thelaser generator 4030 (for example, pulse frequency, fluence, and thelike) to appropriate values for specific types of procedures and/oractuate the valves 4028 to thereby deliver one or more liquid media tothe lumen of the sheath 4014 (for example, a contrast medium, saline, atherapeutic agent, and other liquid media described herein) asappropriate for specific types of procedures, and the secondtranslatable button 4034 may be actuated to translate the laser catheter4012 within the sheath 4014.

In some embodiments, the treatment mode selection system 4018 may takeother forms or include different features. For example, the treatmentmode selection system 4018 may lack electronic components, and the userinput 4022 may be mechanically coupled to the laser catheter 4012 and/orthe valves 4028. Accordingly, actuating the user input 4022 may causethe user input 4022 to translate the laser catheter 4012 relative to thesheath 4014 and/or actuate the valves 4028. As another example, the userinput 4022 may take other forms. For example, the user input 4022 may bea pivotable lever, a depressible button, a rotatable component, or thelike. As a specific example and referring to FIGS. 43-46, a lasercatheter system or kit 4310 is illustrated. The laser catheter system4310 is generally similar to the laser catheter system 4010 and includesa laser catheter (not shown), a sheath 4312, a handle 4314 thattranslatably couples the laser catheter to the sheath 4312, and atreatment mode selection system (not shown). The handle 4314 includes abase portion 4316 that couples to a rotatable and translatable userinput 4318. In some embodiments, the user input 4318 is in operativecommunication with, via a controller (not shown), a prime mover (notshown), and actuation of the user input 4318 causes the prime mover totranslate the laser catheter relative to the sheath 4312 as appropriatefor specific types of procedures. In some embodiments, the user input4318 is mechanically coupled to the laser catheter, and rotation of theuser input 4318 causes translation of the laser catheter relative to thesheath 4312.

Although a large portion of this disclosure includes a discussion oflaser ablation catheters used in conjunction with a sheath assembly toperform CAD and PAD procedures, other the laser ablation catheter andsheath assembly may be used to perform other types of medical and/orsurgical procedures. Laser catheters typically transmit laser energythrough optical fibers housed in a relatively flexible tubular catheterinserted into a body lumen, such as a blood vessel, ureter, fallopiantube, cerebral artery and the like to remove obstructions orrestrictions in the lumen. Catheters used for laser angioplasty andother procedures may have a central passageway or tube which receives aguide wire inserted into the body lumen (for example, vascular system)prior to catheter introduction. The guide wire facilitates theadvancement and placement of the catheter to the selected portion(s) ofthe body lumen for laser ablation of tissue.

The present disclosure, in various aspects, embodiments, andconfigurations, includes components, methods, processes, systems and/orapparatus substantially as depicted and described herein, includingvarious aspects, embodiments, configurations, sub combinations, andsubsets thereof. Those of skill in the art will understand how to makeand use the various aspects, aspects, embodiments, and configurations,after understanding the present disclosure. The present disclosure, invarious aspects, embodiments, and configurations, includes providingdevices and processes in the absence of items not depicted and/ordescribed herein or in various aspects, embodiments, and configurationshereof, including in the absence of such items as may have been used inprevious devices or processes, for example, for improving performance,achieving ease and\or reducing cost of implementation.

The foregoing discussion of the disclosure has been presented forpurposes of illustration and description. The foregoing is not intendedto limit the disclosure to the form or forms disclosed herein. In theforegoing Detailed Description for example, various features of thedisclosure are grouped together in one or more, aspects, embodiments,and configurations for the purpose of streamlining the disclosure. Thefeatures of the aspects, embodiments, and configurations of thedisclosure may be combined in alternate aspects, embodiments, andconfigurations other than those discussed above. This method ofdisclosure is not to be interpreted as reflecting an intention that theclaimed disclosure requires more features than are expressly recited ineach claim. Rather, as the following claims reflect, inventive aspectslie in less than all features of a single foregoing disclosed aspects,embodiments, and configurations. Thus, the following claims are herebyincorporated into this Detailed Description, with each claim standing onits own as a separate preferred embodiment of the disclosure.

Moreover, though the description of the disclosure has includeddescription of one or more aspects, embodiments, or configurations andcertain variations and modifications, other variations, combinations,and modifications are within the scope of the disclosure, for example,as may be within the skill and knowledge of those in the art, afterunderstanding the present disclosure. It is intended to obtain rightswhich include alternative aspects, embodiments, and configurations tothe extent permitted, including alternate, interchangeable and/orequivalent structures, functions, ranges or steps to those claimed,whether or not such alternate, interchangeable and/or equivalentstructures, functions, ranges or steps are disclosed herein, and withoutintending to publicly dedicate any patentable subject matter.

What is claimed is:
 1. A system comprising: a sheath having a proximalend and a distal end and a lumen therein, the lumen being configured totranslatably receive a device having a distal end; a handle coupled tothe sheath; and a treatment mode selection system coupled to the handle,the treatment mode selection system comprising a user input beingactuatable to configure the device from a first configuration to asecond configuration and vice versa, in the first configuration thedistal end of the device being disposed distally from the distal end ofthe sheath, and in the second configuration the distal end of the devicebeing disposed proximally from the distal end of the sheath and withinthe lumen.
 2. The system of claim 4, wherein the user input comprises atranslatable button.
 3. The system of claim 4, wherein the user inputcomprises a rotatable component.
 4. A laser catheter system, comprising:a sheath having a proximal end and a distal end and a lumen therein; alaser catheter translatably disposed within the sheath, the lasercatheter comprising: a proximal end configured to couple to a lasergenerator; a distal end; at least one emitter configured to couple tothe laser generator, a handle coupled to the sheath and translatablycoupled to the laser catheter; a treatment mode selection system coupledto the sheath, the treatment mode selection system comprising a userinput being actuatable to configure the laser catheter system from afirst configuration to a second configuration and vice versa, in thefirst configuration the distal end of the laser catheter being disposeddistally from the distal end of the sheath, and in the secondconfiguration the distal end of the laser catheter being disposedproximally from the distal end of the sheath and within the lumen andthereby creating a cavity between the distal end of the laser catheterand the distal end of the sheath.
 5. The laser catheter system of claim4, wherein the user input is actuatable to configure at least oneoperating parameter of the laser generator.